U.S. patent application number 12/917661 was filed with the patent office on 2011-05-26 for multi-array, multi-specific electrochemiluminescence testing.
This patent application is currently assigned to MESO SCALE TECHNOLOGY LLP. Invention is credited to Mark A. Billadeau, Ramin Darvari, Alan Fischer, Liang-Hong Guo, Larry R. Helms, Jon Leland, Mark T. Martin, George B. Sigal, James L. Wilbur, Jacob N. WOHLSTADTER.
Application Number | 20110124116 12/917661 |
Document ID | / |
Family ID | 46203207 |
Filed Date | 2011-05-26 |
United States Patent
Application |
20110124116 |
Kind Code |
A1 |
WOHLSTADTER; Jacob N. ; et
al. |
May 26, 2011 |
MULTI-ARRAY, MULTI-SPECIFIC ELECTROCHEMILUMINESCENCE TESTING
Abstract
Materials and methods are provided for producing patterned
multi-array, multi-specific surfaces for use in diagnostics. The
invention provides for electrochemiluminescence methods for
detecting or measuring an analyte of interest. It also provides for
novel electrodes for ECL assays. Materials and methods are provided
for the chemical and/or physical control of conducting domains and
reagent deposition for use multiply specific testing
procedures.
Inventors: |
WOHLSTADTER; Jacob N.;
(Potomac, MD) ; Wilbur; James L.; (Boyds, MD)
; Sigal; George B.; (Rockville, MD) ; Martin; Mark
T.; (Rockville, MD) ; Guo; Liang-Hong;
(Gaithersburg, MD) ; Fischer; Alan; (Cambridge,
MA) ; Leland; Jon; (Silver Spring, MD) ;
Billadeau; Mark A.; (Middletown, MD) ; Helms; Larry
R.; (Germantown, MD) ; Darvari; Ramin;
(Waltham, MA) |
Assignee: |
MESO SCALE TECHNOLOGY LLP
Gaithersburg
MD
|
Family ID: |
46203207 |
Appl. No.: |
12/917661 |
Filed: |
November 2, 2010 |
Related U.S. Patent Documents
|
|
|
|
|
|
Application
Number |
Filing Date |
Patent Number |
|
|
11264535 |
Oct 31, 2005 |
7824925 |
|
|
12917661 |
|
|
|
|
10693441 |
Oct 24, 2003 |
7015046 |
|
|
11264535 |
|
|
|
|
08932110 |
Sep 17, 1997 |
6673533 |
|
|
10693441 |
|
|
|
|
08715163 |
Sep 17, 1996 |
6207369 |
|
|
08932110 |
|
|
|
|
08611804 |
Mar 6, 1996 |
6066448 |
|
|
08715163 |
|
|
|
|
08402076 |
Mar 10, 1995 |
|
|
|
08611804 |
|
|
|
|
08402277 |
Mar 10, 1995 |
|
|
|
08402076 |
|
|
|
|
Current U.S.
Class: |
436/172 |
Current CPC
Class: |
Y10S 436/806 20130101;
B01L 3/5027 20130101; B01L 2300/0636 20130101; Y10S 435/808
20130101; G01N 21/76 20130101; B01L 3/502715 20130101; G01N 21/66
20130101; B82Y 15/00 20130101; Y10S 435/817 20130101; G01N 33/54313
20130101; G01N 33/5438 20130101; C12Q 1/6825 20130101; Y10S 436/807
20130101; B82Y 30/00 20130101; G01N 33/582 20130101; G01N 21/253
20130101; B01L 2300/0645 20130101; Y10S 436/805 20130101; G01N
33/585 20130101 |
Class at
Publication: |
436/172 |
International
Class: |
G01N 21/76 20060101
G01N021/76 |
Claims
1. An electrode for use in the detection of an analyte by
electrochemiluminescence comprising a composite containing a
polymer matrix and a multiplicity of carbon particles dispersed
therein, said electrode having a binding domain containing a
reagent capable of binding a component of a binding
electrochemiluminescence assay.
2-139. (canceled)
Description
[0001] This application is a continuation-in-part of copending
application Ser. No. 08/715,163 filed Sep. 17, 1996 which is a
continuation-in-part of copending application Ser. No. 08/611,804
filed Mar. 6, 1996, which is a continuation-in-part of copending
application Ser. Nos. 08/402,076 filed Mar. 10, 1995 and 08/402,277
filed Mar. 10, 1995, each of which is incorporated by reference
herein in its entirety.
1. INTRODUCTION
[0002] The present invention provides for a patterned multi-array,
multi-specific surface (PMAMS) for electrochemiluminescence based
tests, as well as methods for making and using PMAMS.
2. BACKGROUND OF THE INVENTION
2.1. Diagnostic Assays
[0003] There is a strong economic need for rapid sensitive
diagnostic technologies. Diagnostic technologies are important in a
wide variety of economic markets including health care, research,
agricultural, veterinary, and industrial marketplaces. An
improvement in sensitivity, time required, ease of use, robustness,
or cost can open entirely new diagnostic markets where previously
no technology could meet the market need. Certain diagnostic
technologies may possess high sensitivity but are too expensive to
meet market needs. Other techniques may be cost effective but not
robust enough for various markets. A novel diagnostic technique
which is capable of combining these qualities is a significant
advance and opportunity in the diagnostics business.
[0004] There are a number of different analytical techniques used
in diagnostic applications. These techniques include radioactive
labeling, enzyme linked immunoassays, chemical colorimetric assays,
fluorescence labeling, chemiluminescent labeling, and
electrochemiluminescent labeling. Each of these techniques has a
unique combination of sensitivity levels, ease of use, robustness,
speed and cost which define and limit their utility in different
diagnostic markets. These differences are in part due to the
physical constraints inherent to each technique. Radioactive
labeling, for example, is inherently non-robust because the label
itself decays and the disposal of the resulting radioactive waste
results in economic, safety and environmental costs for many
applications.
[0005] Many of the sensitive diagnostic techniques in use today are
market-limited primarily because of the need for skilled
technicians to perform the tests. Electrochemiluminescent
procedures in use today, for example, require not only skilled
technicians but repeated washing and preparatory steps. This
increases both the costs and the need for waste disposal. Novel
diagnostics which simplify the testing procedures as well as
decrease the cost per test will be of great importance and utility
in opening new markets as well as improving performance in existing
markets.
2.2. Electrochemiluminescence
[0006] Electrochemiluminescence ("ECL") is the phenomena whereby an
electrically excited species emits a photon (see, e.g., Leland and
Powell, 1990 J. Electrochem. Soc. 137(10):3127-3131). Species from
which ECL can be induced are termed ECL labels and are also
referred to herein as TAGs. Commonly used ECL labels include:
organometallic compounds where the metal is from, for example, the
noble metals of group VIII, including Ru-containing and
Os-containing organometallic compounds such as the
Ru(2,2'-bipyridine).sub.3.sup.2+ moiety (also referred to as
"Rubpy" or TAG1), disclosed, e.g., by Bard et al. (U.S. Pat. No.
5,238,808). "TAG1" and "Rubpy" also refer to derivatives of
Ru(2,2'-bipyridine).sub.3.sup.2+. Fundamental to ECL-based
detection systems is the need for an electrical potential to excite
the ECL label to emit a photon. An electrical potential waveform is
applied across an electrode surface, typically a metal surface, and
a counterelectrode (see e.g., U.S. Pat. Nos. 5,068,088, 5,093,268,
5,061,445, 5,238,808, 5,147,806, 5,247,243, 5,296,191, 5,310,687,
5,221,605). The ECL is promoted to an excited state as a result of
a series of chemical reactions triggered by the electrical energy
received from the working electrode. A molecule which promotes ECL
of the TAG is advantageously provided, such as oxalate or, more
preferably, tripropylamine (see U.S. Pat. No. 5,310,687).
[0007] The excitation of a TAG in an ECL reaction typically
involves diffusion of the TAG molecule to the surface of an
electrode. Other mechanisms for the excitation of a TAG molecule by
an electrode include the use of electrochemical mediators in
solution (Haapakka, 1982, Anal Chim. Acta, 141:263) and the capture
of beads presenting TAG molecules on an electrode (PCT published
applications WO 90/05301 and WO 92/14139). Alternatively, ECL has
been observed from TAG that was adsorbed directly on the surface of
working electrodes (U.S. Pat. No. 5,324,457), e.g., by non-specific
adsorption (Xu et al., 1994, Langmuir, 10:2409-2414), by
incorporation into L-B films (Zhang et al., 1988, J. Phys. Chem.,
92:5566), by incorporation into self-assembled monolayers (Obeng et
al., 1991, Langmuir, 7:195), and by incorporation into thick
(micrometer) films (Rubenstein et al., 1981, J. Am. Chem. Soc.,
102:6641). Similarly, Xu et al. (PCT published application WO
96/06946) have observed ECL from TAG molecules intercalated into
DNA strands when such strands were adsorbed onto gold electrodes by
interaction with aluminum centers immobilized on a self-assembled
monolayer of alkanethiolates.
[0008] Various apparatus well known to the art are available for
conducting and detecting ECL reactions. For example, Zhang et al.
(U.S. Pat. No. 5,324,457) discloses exemplary electrodes for use in
electrochemical cells for conducting ECL. Leventis et al. (U.S.
Pat. No. 5,093,268) discloses electrochemical cells for use in
conducting ECL reactions. Kamin et al. (U.S. Pat. No. 5,147,806)
discloses apparatus for conducting and detecting ECL reactions,
including voltage control devices. Zoski et al. (U.S. Pat. No.
5,061,445) discloses apparatus for conducting and detecting ECL
reactions, including electrical potential waveform diagrams for
eliciting ECL reactions, digital to analog converters, control
apparatus, detection apparatus and methods for detecting current
generated by an ECL reaction at the working electrode to provide
feedback information to the electronic control apparatus.
2.3. Commercial ECL Assays
[0009] The light generated by ECL labels can be used as a reporter
signal in diagnostic procedures (Bard et al., U.S. Pat. No.
5,221,605). For instance, an ECL label can be covalently coupled to
a binding agent such as an antibody or nucleic acid probe. The ECL
label/binding agent complex can be used to assay for a variety of
substances (Bard et al., U.S. Pat. No. 5,238,808). The use of ECL
in assays is reviewed in detail by, for example, Knight et al.,
1994, Analyst, 119:879-890. In brief, the ECL technique may be used
as a method of detecting in a volume of a sample an analyte of
interest present in the sample in relatively small
concentrations.
[0010] To date, all commercial ECL assays are carried out on
centimeter scale electrode surfaces. The centimeter scale
electrodes strike a balance between the enhanced magnitude of an
ECL signal resulting from larger electrodes and the desirability of
decreasing the total sample volume necessary for each assay.
However, even centimeter scale electrodes fail to achieve the
sensitivity required for many assays. In an attempt to overcome
this problem, all commercial ECL systems further enhance
sensitivity by using coated magnetic beads to capture ECL analytes
or reagents. The beads are then moved adjacent to a working
electrode for enhanced sensitivity.
[0011] However, the currently available technology has many
limitations (primarily cost and complexity) that restrict its use
in low cost assays employing disposable cartridges as well as its
use in high throughput systems that perform multiple assays
concurrently.
[0012] Leventis et al. (U.S. Pat. No. 5,093,268) has proposed a
method of assaying more than one different analyte simultaneously
by the use of different ECL labels for each analyte, each emitting
photons at different wavelengths for each different analyte in a
single assay. However, this technique is limited, for example, by
the unavailability of a sufficient number of effective ECL labels
radiating at different wavelengths and the need to optimize the
chemical conditions for each ECL label. These practical constraints
have prevented the commercialization of such multi-wavelength,
multi-analyte ECL detection systems.
[0013] Commercial methods for conducting ECL assays also require
that the assay cell, including the electrodes, must be cleaned by
any one of a number of methods, including the use of dilute acids,
dilute bases, detergent solutions, and so forth as disclosed, for
example, by U.S. Pat. No. 5,147,806.
2.4. Objects of the Invention
[0014] It is therefore an object of the present invention to
provide a novel, cost effective electrode and disposable for
conducting ECL assays.
[0015] It is a further object of the present invention to provide a
novel and cost effective system for conducting a plurality of ECL
assays, either sequentially or simultaneously and in a preferred
embodiment, providing built-in control standards for improved
accuracy.
[0016] It is a further object of the present invention to provide a
cassette comprising one or more supports suitable for conducting a
plurality of simultaneous or sequential ECL assays that is also
disposable.
[0017] It is a further and related object of this invention to
reduce the time and cost of conducting individual assays for
analytes of interest in biological samples.
[0018] It is still a further and related object of this invention
to provide methods and apparatus for conducting a plurality of
simultaneous assays for a plurality of analytes of interest in a
single biological sample.
3. SUMMARY OF THE INVENTION
[0019] The invention relates to a cassette for conducting ECL
reactions and assays comprising one or more binding domains
immobilized on a support. The support may act as an electrode for
generating electrochemiluminescence. Alternatively, one or more
electrodes may be on additional supports, and said electrodes may
be brought into proximity to the first support so as to generate
ECL. The cassette may have one or more electrodes or one or more
electrode/counterelectrode pairs. The cassette may also comprise a
second support capable of being placed adjacent to the first
support to provide sample containing means therebetween, and/or
serve as an electrode. The binding domains are patterned on a
support surface and are prepared so as to bind analytes or reagents
of interest.
[0020] The invention further relates to novel, disposable
electrodes amenable to use in a disposable format. These electrodes
can be comprised of various forms of carbon such as glassy carbon,
carbon black or carbon (graphitic) nanotubes.
[0021] The invention further relates to composite electrodes, i.e.
electrodes comprised of more than one material. These electrodes
can be tailored to control performance, cost and manufacturability
to make them amenable to use in a disposable format.
[0022] The invention further relates to assays in which particles
are used as solid-phase supports for binding reagents. Said
particles are captured on a porous electrode by filtration and
analytes are detected. Kits based on pre-prepared conducting
filters with particles are described.
[0023] The invention further relates to electrodes that can be used
to resolve two or more ECL signals. Methods for the modification of
electrodes are also described.
[0024] The invention further relates to an apparatus for measuring
electrochemiluminescence of a sample that provides support or
cassette handling means, voltage control means adapted to apply a
controlled voltage waveform effective to trigger
electrochemiluminescence, photon detector means for detecting
electrochemiluminescence from the sample and sample handling
means.
[0025] The invention further relates to methods for using the
cassettes for measuring electrochemiluminescence in a sample by
contacting the plurality of binding domains of a cassette with a
sample which contains a plurality of analytes of interest, under
ECL assay conditions, and then applying a voltage waveform
effective to trigger electrochemiluminescence and detecting or
measuring of the triggered electrochemiluminescence.
[0026] The invention also provides for kits comprising components
including cassettes suitable for simultaneously measuring a
plurality of electrochemiluminescence reactions, support surfaces
and upon which a plurality of domains are immobilized assay, media
for conduct of the ECL assay conducting chemical reactions.
[0027] The invention is also in rapid disposable
electrochemiluminescence assays. Commercial ECL assays are
performed using a flow cell with a working and counter electrode. A
disposable electrode, as disclosed herein, does not require washing
and/or cleaning to eliminate carry-over and regenerate a uniform
electrode surface as does a permanent flow cell electrode.
[0028] The invention also provides for increased kinetics through
the use of porous electrodes. Formatted and/or porous disposable
electrodes are used to rapidly produce assay results. Assay results
with disposable electrodes may be achieved in less than an hour. In
preferred embodiments ECL assay results from disposable electrodes
may be achieved in less than 30 minutes and in some cases less than
15 minutes. In the most preferred embodiments, the assay results
can be achieved in less than 5 minutes or in the most advantageous
case, than 1 minute. In multi-assay formats of the invention more
than one ECL assay result may be achieved in such time periods or
less. Kits for rapid disposable ECL systems are disclosed.
[0029] Additionally, the invention provides for portable ECL
diagnostic instruments. Cartridges or kits for portable ECL
diagnostics may use the novel disposable electrodes and reagent
packs. PMAMS and electrodes for ECL assays may be packaged as kits
for use in portable ECL instrument readers. Such kits and ECL
instrument readers may be used to achieve assay results in short
time periods. Assay results may be achieved in the very short time
periods discussed above.
4. DESCRIPTION OF THE FIGURES
[0030] FIG. 1 illustrates a cassette according to the invention
wherein a plurality of binding domains are present on an
electrode.
[0031] FIG. 1A illustrates two supports forming a cassette
according to the invention wherein a plurality of binding domains
14 are present on support 10 and a plurality of corresponding
electrodes 16 is present on support 12 so that approximation of the
supports places an electrode pair adjacent to each binding
domain.
[0032] FIG. 2 illustrates two supports forming a cassette according
to the invention wherein a plurality of binding domains 30 on
support 26 are adjacent to each of single electrodes 32 so that
approximating supports 26 and 28 places each of counterelectrodes
38 adjacent to each of binding domains 30.
[0033] FIG. 3 illustrates two supports forming a cassette according
to the invention wherein a plurality of binding domains 48 have
electrode counterelectrode pairs 50 adjacent thereto on support 44.
Support 46 may optionally be placed adjacent to support 44 so that
support 46 provides sample containing means adjacent to binding
domains 48 and electrodes 50.
[0034] FIG. 4 illustrates two supports forming a cassette according
to the invention wherein a plurality of binding domains 64 on
support 60 are contacted with a sample suspected of containing an
analyte. Support 62 has regions 66 containing reaction medium for
detecting or measuring an analyte of interest or for carrying out a
desired reaction so that approximating support 60 and support 62
causes binding domains 64 and regions 66 to contact one
another.
[0035] FIG. 5A illustrates a top view of patterned binding domains
for a multi-array, multi-specific binding surface. Geometric
shapes, triangles, squares and circles, represent binding domains
specific for different analytes. The binding domains may be
hydrophobic or hydrophilic. The surrounding surface may have the
opposite property (hydrophilic or hydrophobic) of the binding
domains to minimize spreading of binding reagents or analyte from
the binding domains.
[0036] FIG. 5B illustrates a top view of a microfluidics guide for
delivering binding reagents and/or analytes to discrete binding
domains. Each dot illustrates a cross section of a microfluidics
guide (e.g., a capillary).
[0037] FIG. 5C illustrates a side view of a microfluidics guide
showing the approximation of registered or aligned microfluidic
guides for delivering binding reagents and/or analytes to a multi
array of patterned binding domains. Each microfluidic guide may
deliver a different binding reagent to a discrete binding
domain.
[0038] FIG. 6A illustrates the approximation of a multi-array of
electrodes in register with a surface having patterned multi-array,
multi-specific binding domains. A removable electrode protection
barrier is shown between the electrode array and the binding
surface array. The entire assembly comprises a cassette for
conducting a plurality of ECL reactions.
[0039] FIG. 6B illustrates the approximation of an array of
registered or aligned addressable working and counterelectrodes.
The electrodes may be shape complementary with the binding domain
or of other shapes (e.g., interdigitating).
[0040] FIG. 7 illustrates the side view of an approximated array of
registered or aligned addressable working and counterelectrodes and
the complementary binding surface wherein conducting polymers are
grown from the surfaces of the electrodes across the gap between
the electrode array and the binding domains so as to extend the
potential field around the ECL label of the sample to increase the
efficiency of the ECL reaction.
[0041] FIG. 8 illustrates the side view of an approximated array of
registered or aligned addressable working and counterelectrodes and
the complementary binding surface with conducting particles
interspersed between both components to extend the potential field.
By extending the potential field around the ECL label of the sample
the efficiency of the ECL reaction is enhanced. The conducting
particles can be magnetic to permit ready manipulation.
[0042] FIG. 9 illustrates the side view of an approximated array of
registered or aligned addressable working and counterelectrodes and
the complementary binding surface wherein the electrodes have fine
projections extending into the gap between the electrode surface
and the binding domains in order to extend the potential field
around the ECL label of the sample, to increase the efficiency of
the ECL reaction.
[0043] FIG. 10 illustrates the side view of an approximated array
of registered or aligned addressable working and counterelectrodes
and the complementary binding surface where the surfaces are not
parallel, but are instead conformed one to the other in a
complementary fashion.
[0044] FIG. 11 illustrates the side view of a support having a
metallic layer thereon to provide a single electrode and binding
surface assembly in the form of a cassette. An array of
self-assembled monolayers ("SAMs") is patterned on the metallic
layer.
[0045] FIG. 12 illustrates the side view of a support having a
metallic layer thereon to provide a single electrode and binding
surface assembly in the form of a cassette. An array of SAMs is
patterned on the metallic layer and conducting microparticles are
shown interspersed among the patterned SAMs so as to extend the
potential field around the ECL label of the sample, to increase the
efficiency of the ECL reaction.
[0046] FIG. 13 illustrates the side view of a support having a
metallic layer thereon to provide a single electrode and binding
surface assembly in the form of a cassette. An array of self
assembled monolayers or SAMs is patterned on the metallic layer and
the growth of a conducting polymer and/or fiber from the ECL label
so as to extend the potential field around the ECL label of the
sample to increase the efficiency of the ECL reaction, is
illustrated.
[0047] FIG. 14 is a diagram of a support having an array of
electrode pairs controlled by a computer.
[0048] FIG. 15 is a diagram of a support having an array of
electrode pairs.
[0049] FIG. 16 is a diagram of a support having an array of
electrode pairs and computer system for controlling the
energization of each electrode pair.
[0050] FIG. 17 is a diagram of a support having an array of
electrode pairs and a computer system with a plurality of voltage
sources and multiplexers for controlling the energization of each
electrode pair.
[0051] FIG. 18 is a diagram of a support having an array of
electrode pairs and a computer system with a plurality of switched
voltage sources for controlling the energization of each electrode
pair.
[0052] FIGS. 19(a)-(e) are plan views of several alternative
electrode-counterelectrode pair combinations.
[0053] FIG. 20 illustrates a support with a completed sandwich
assay.
[0054] FIG. 21 illustrates two opposing PMAMS surfaces on
supports.
[0055] FIG. 22A illustrates an array of microfluidics guides (2201)
and a fibril mat (2200).
[0056] FIG. 22B illustrates binding domains (2202) on a fibril mat
(2200).
[0057] FIG. 23A illustrates an apparatus for forming a fibril mat
by vacuum filtration.
[0058] FIG. 23B illustrates a fibril mat (2304) on a filter
membrane (2303).
[0059] FIG. 24 illustrates the use of rollers to produce fibril
mats.
[0060] FIG. 25 shows a schematic of a multi-layer fibril mat, in
which the upper layer has binding domains used for assays.
[0061] FIG. 26 shows a schematic of a fibril derivatized with
moieties that enhance non-specific binding, and several species,
both biological and non-biological are bound to the surface.
[0062] FIG. 27 shows a schematic of a fibril derivatized with
moieties that enhance non-specific binding and several species
bound to a derivatized fibril with some species additionally bound
to ligands.
[0063] FIG. 28 illustrates several species covalently attached to a
fibril and some species are further bound to additional
entities.
[0064] FIG. 29 illustrates the use of a multilayer fibril mat as an
optical filter that, depending on the position of a source of light
on or within the mat, may allow light to pass and/or may absorb
and/or scatter light.
[0065] FIG. 30A illustrates cyclic voltammograms from
electrochemical measurements on carbon fibril mat electrodes.
[0066] FIG. 30B illustrates cyclic voltammograms from
electrochemical measurements on gold foil electrodes.
[0067] FIG. 31 compares an electrochemical property of fibril mats
as a function of the thickness of the mat and the scan rate.
[0068] FIG. 32 shows a plot that illustrates that non-specific
binding on fibrils generally increases as the concentration of
fibrils in a protein solution increases.
[0069] FIG. 33 demonstrates that the use of surfactants can reduce
non-specific binding between ECL-TAG1-labeled protein and carbon
fibrils.
[0070] FIG. 34 shows a schematic of a top view of an experimental
cell used to measure electrochemical properties and ECL on a fibril
mat electrode.
[0071] FIG. 35 shows an ECL signal obtained using a fibril mat as
an electrode and 1000 pM TAG1 (solid line) in solution and a signal
from assay buffer (no TAG1) (dashed line).
[0072] FIG. 36 shows a schematic of a two surface PMAMS device, in
which two arrays of supported electrodes are separated by a
patterned dielectric layer.
[0073] FIG. 37 illustrates an apparatus with a plurality of binding
domains (3702) on one support and an electrode and counterelectrode
on another support.
[0074] FIG. 38 shows a cassette where binding domains are presented
on the surfaces of distinct objects supported on the counter
electrode.
[0075] FIG. 39 shows a gel in contact with a working and
counterelectrode.
[0076] FIG. 40 shows a graph of ECL intensity and a cyclic
voltammogram from an ECL labeled gel in contact with a working and
counterelectrode.
[0077] FIG. 41 shows a graph of ECL intensity and a cyclic
voltammogram from a non-ECL labeled gel in contact with a working
and counterelectrode.
[0078] FIG. 42 shows a schematic for a two-surface cassette used
for ECL.
[0079] FIG. 43 demonstrates that fibril mats can be used as
electrodes for ECL of Antibody-TAG1 adsorbed to the mats.
[0080] FIG. 44A shows ECL intensity of a TAG1 labeled protein
immobilized on an electrode.
[0081] FIG. 44B shows the cyclic voltammogram of a coated
electrode.
[0082] FIG. 45A shows quasi-reversible repetitive generation of ECL
signal from an immobilized ECL TAG1 labeled protein.
[0083] FIG. 45B shows the cyclic voltammogram of a coated electrode
indicating partial preservation of the coating.
[0084] FIG. 46A shows irreversible generation of ECL signal from an
immobilized ECL TAG1 labeled protein.
[0085] FIG. 46B shows the cyclic voltammogram of a coated electrode
indicating substantial loss of the coating.
[0086] FIG. 47 shows a multi-array ECL apparatus and a
microprocessor containing controller means for generating and
analyzing ECL signals.
[0087] FIG. 48 shows the dose response for an AFP immunoassay that
involves formation of a sandwich complex on streptavidin-coated
Dynal beads, capture of the beads on a fibril mat electrode, and
detection of the bound complex by ECL.
[0088] FIG. 49 shows the dose response for an AFP immunoassay that
involves the formation of a sandwich complex on streptavidin-coated
silica particles, the capture of the particles on a fibril mat
electrode, and detection of the bound complex by ECL.
[0089] FIG. 50 shows a schematic describing the use of a SAM for
immobilizing binding reagents on a surface.
[0090] FIG. 51 shows the dose response for an AFP immunoassay that
involves the formation of a sandwich complex on a
streptavidin-coated SAM of alkanethiolates on a gold electrode, and
detection of the bound complex by ECL.
[0091] FIG. 52 illustrates the presentation of TAG moieties to the
working electrode in a "Two Surface" assay.
[0092] FIG. 53 shows the dose response for an AFP immunoassay that
involves formation of a sandwich complex on a streptavidin-coated,
oxidized, EVA-fibril composite and detection of the bound complex
by ECL.
[0093] FIG. 54 shows the dose response for a nucleic acid
hybridization assay that involves formation of a nucleic acid
sandwich complex on a streptavidin-coated, oxidized, EVA-fibril
composite and detection of the bound complex by ECL.
[0094] FIG. 55 shows the dose response for a DNA assay that
involves hybridization of a biotin-labeled oligonucleotide to a
TAG1 labeled oligonucleotide, capture of the complex on a
streptavidin-coated fibril mat electrode and detection of the bound
complex by ECL.
[0095] FIG. 56 shows the dose response for an AFP assay that
involves the formation of a sandwich complex on a
streptavidin-coated, UTFM on a nylon membrane and detection of the
bound complex by ECL.
[0096] FIG. 57 shows the dose response for an AFP assay that
involves the formation of a sandwich complex on a
streptavidin-coated UTFM formed on a gold-coated nylon membrane and
detection of the bound complex by ECL.
[0097] FIG. 58 illustrates an ECL signal in which the
electrochemical potential for one or more components is
shifted.
[0098] FIG. 59 illustrates an ECL signal in which the intensity of
the ECL signal for one or more components of the sample is reduced
relative to the ECL signal for other components of the sample.
[0099] FIG. 60 shows an ECL trace of a sample that is ECL assay
buffer.
[0100] FIG. 61 shows an ECL trace of a sample that contains
AFP.
[0101] FIG. 62 shows a plot of the ECL signal (S-B, the difference
between the ECL Signal (S) and the background signal (B)) as a
function of the concentration of AFP (IU/mL) for an AFP assay. The
ECL mediated AFP assay was conducted using plasma treated
fibril-polymer composites as a support for binding reagents and as
a working electrode.
[0102] FIG. 63 shows a plot of the ECL signal (S-B, the difference
between the ECL Signal (S) and the background signal (B)) as a
function of the concentration of AFP (IU/mL) for an AFP assay. The
ECL mediated AFP assay was conducted using plasma treated
fibril-polymer composites as a support for binding reagents and as
a working electrode.
[0103] FIG. 64 shows a plot of the ECL signal (S-B, the difference
between the ECL Signal (S) and the background signal (B)) as a
function of the concentration of AFP (IU/mL) for an AFP assay. The
ECL mediated AFP assay was conducted using plasma treated
fibril-polymer composites (15% fibrils by weight) as a support for
binding reagents and as a working electrode.
[0104] FIG. 65 shows a plot of the ECL signal (S-B, the difference
between the ECL Signal (S) and the background signal (B)) as a
function of the concentration of AFP (IU/mL) for an AFP assay. The
ECL mediated AFP assay was conducted using plasma treated
fibril-polymer composites as a support for binding reagents and as
a working electrode.
[0105] FIG. 66 shows a plot of the ECL signal (S-B, the difference
between the ECL Signal (S) and the background signal (B)) as a
function of the concentration of AFP (IU/mL) for an AFP assay. The
ECL mediated AFP assay was conducted using plasma treated
fibril-polymer composites as a support for binding reagents and as
a working electrode.
[0106] FIG. 67 shows a plot of the ECL signal (S-B, the difference
between the ECL Signal (S) and the background signal (B)) as a
function of the concentration of AFP (IU/mL) for an AFP assay. The
ECL mediated AFP assay was conducted using dry reagents and without
a wash step.
[0107] FIG. 68 shows a schematic diagram of an assay cell according
to an embodiment of the present invention.
[0108] FIG. 69 shows a schematic diagram of an assay system
according to another embodiment of the present invention.
5. DETAILED DESCRIPTION OF THE INVENTION
[0109] Accordingly, the invention includes in a broad aspect
cassettes for conducting one or more electrochemiluminescence
assays. The cassettes are formed of supports having thereon a
plurality of binding domains able to specifically bind one or more
analytes of interest. The binding domains are prepared as
patterned, multi-array multi-specific surfaces ("PMAMS") on the
support. The PMAMS offer a significant improvement from ECL assay
methods previously known by, e.g., greatly increasing the density
of assays that can be performed and allowing for a plurality of
different assays that may be rapidly or simultaneously
performed.
[0110] The cassette may include a plurality of electrodes able to
selectively trigger ECL emission of light from ECL labeled reagents
bound to the binding domains. FIG. 47 shows an multi-array ECL
apparatus using a cassette 4700 which comprises a housing 4717,
electrical connections to the electrode in the cassette 4718, a
waveform generator or potentiostat 4719, a CCD camera for imaging
the ECL emitted from the PMAMS 4720, and a microcomputer for
controlling the waveform generator and analyzing the image received
by the camera 4721.
[0111] In the embodiment of the invention shown in FIG. 1, a
cassette 180 comprises a working electrode comprising a conducting
material 181 on a support material 182. A plurality of binding
domains, i.e. a PMAMS 183 are present on the electrode 181. The
cassette also includes a means for introducing samples and reagents
(fluid channel 184) and a counter electrode 185. A reference
electrode 186 may also be included.
[0112] In another embodiment, a plurality of working electrodes are
used to simultaneously generate an ECL signal at a plurality of
binding domains. In this embodiment, the ECL signal from each
binding domain is identified without the use of light imaging
equipment.
[0113] In certain embodiments of the invention, it is desirable to
reproducibly immobilize a specified or predetermined amount of one
or more reagents on a surface. Immobilization broadly applies to
any method by which a reagent is attached to a surface, including
but not limited to: covalent chemical bonds; non-specific
adsorption; drying a reagent on a surface; electrostatic
interactions; hydrophobic and/or hydrophilic interactions;
confinement or entrainment in liquids or gels; biospecific binding,
(e.g., ligand/receptor interactions or hybridization of
oligonucleotides); metal/ligand bonds; chelation, and/or
entanglement in polymers.
[0114] The amount of reagent immobilized on a surface may be
predetermined in several ways. For example, the amount of reagent
on a surface may be specified by one or more volume and/or area
elements in which the reagent is present. It may also be specified
by the number of individual molecules of a reagent that are
immobilized on a surface. The amount of reagent may be specified in
terms of the density of a particular reagent in a given region. The
amount of reagent may be specified as a percentage of a surface
bearing a particular reagent, either with regard to the total area
of the surface, or relative to the amounts of other reagents
present on the surface. The amount of reagent may also be defined
as the quantity of reagent that must be present on a particular
surface to give sufficient ECL intensity so as to make an assay
achieve a desired specificity. In a specific example, a 1 cm.sup.2
area of a gold surface may be coated with a monolayer of
alkanethiols.
[0115] Reagents may also be reproducibly immobilized on coated
surfaces. The coating may serve to enhance immobilization for some
reagents and/or reduce or prohibit immobilization for other
reagents. The surface may be completely coated or the surface may
be partially coated (i.e. a patterned coating). The coating may be
uniform in composition, or it may contain elements of different
composition. In a specific example, the coating may be a patterned
monolayer film that immobilizes immunoglobulin G via covalent
chemical bonds in some areas, and prevents its immobilization in
others.
[0116] The coating may also serve to predetermine the amount(s) of
one or more reagents immobilized on the surface in subsequent steps
or processes. Alternatively, the amount of a particular reagent may
be controlled by limiting the amount of reagent that is
deposited.
[0117] Having a surface that has reagents (or a coating)
immobilized in a quantitative, reproducible fashion gives the
ability to reproducibly and quantitatively measure an ECL signal
from a sample, thus allowing calibration.
[0118] Broadly, the assays conducted using cassettes according to
the invention are assays that benefit from the use of a plurality
of discrete binding domains. For example, use of such cassettes
allows rapid and/or concurrent detection or measurement of a wide
variety of analytes of interest. In a preferred embodiment, the
assays according to the invention are also those that benefit from
the use of an ECL labeled reagent, analyte or binding surface. An
ECL assay according to the invention comprises contacting a
plurality of binding domains with a sample suspected of containing
an analyte of interest and triggering an ECL emission from a bound
ECL label, wherein the ECL label is on the analyte or a competitor
of the analyte, on a reagent that binds to the analyte or on the
plurality of binding domains.
[0119] The invention provides for ECL assay methods for detecting
or measuring an analyte of interest, comprising (a) contacting one
or more binding domains immobilized on an electrode, in which said
contacting is with a sample comprising molecules leveled to an ECL
label, (b) applying a voltage waveform effective to trigger ECL at
said binding domains, and (c) measuring or detecting ECL.
[0120] The term sample is used in the broadest sense. It includes a
quantity of any substance to be used in the methods of the
invention. By way of non-limiting examples it may include a portion
of a material to be assayed containing an analyte-of-interest, a
pre-processed or prepared part thereof or a quantity of reagents to
be used in the method of the invention.
[0121] The invention also provides ECL assay methods for detecting
or measuring an analyte of interest, comprising (a) contacting one
or more binding domains, said binding domains being immobilized on
a surface of one or more supports, in which said contacting is with
a sample comprising molecules linked to an electrochemiluminescent
label; (b) bringing an electrode into proximity to said binding
domains; and (c) applying a voltage waveform effective to trigger
ECL at said binding domains; and detecting or measuring ECL.
[0122] In another embodiment, the invention provides ECL assay
methods for (a) contacting one or more binding domains, said
plurality of binding domains (i) being immobilized on a surface of
one or more supports, and (ii) being spatially aligned with and in
proximity to a plurality of electrode and counterelectrode pairs,
in which said contacting is with a sample comprising molecules
linked to an electrochemiluminescent label; (b) bringing an
electrode and counterelectrode into proximity to said binding
domains; (c) applying a voltage waveform effective to trigger
electrochemiluminescence at said binding domains; and (d) detecting
or measuring electrochemiluminescence.
[0123] The invention provides a method of detecting in a volume of
a multicomponent, liquid sample a plurality of analytes of interest
which may be present in the sample at various concentrations.
[0124] Broadly a plurality of analytes may be detected from a
multicomponent sample in less than 10.sup.-3 molar concentrations.
Preferably a plurality of analytes may be detected at less than
10.sup.-12 molar concentrations from a multicomponent sample.
[0125] The invention provides for detection from a multicomponent
sample which may be performed as heterogeneous assays, i.e., assays
in which a plurality of unbound labeled reagents are separated from
a plurality of bound labeled reagents prior to exposure of the
bound labeled reagents to electrochemical energy, and homogeneous
assays, i.e., assays in which a plurality of unbound labeled
reagents and bound labeled reagents are exposed to electrochemical
energy together.
[0126] In the assays of the present invention, the electromagnetic
radiation used to detect a particular analyte is distinguishable
from the electromagnetic radiation corresponding to other analytes
by identifying its position and/or location as one or more features
of a pattern, said pattern corresponding to the pattern of the
binding domains in the PMAMS.
[0127] In the homogeneous assays of the present invention, the
electromagnetic radiation emitted by the bound labeled reagents
either as an increase or as a decrease in the amount of
electromagnetic radiation emitted by the bound labeled reagents in
comparison to the unbound reagents, or by detection of
electromagnetic radiation emitted from sources corresponding in
space to one or more features of a pattern corresponding to the
pattern of the binding domains in the PMAMS.
[0128] In a specific example of the method of the invention shown
in FIG. 20, a sandwich assay is conducted on a support (5) with a
plurality of binding domains (BD) on its surface that are specific
for binding a particular analyte (An). When a sample suspected of
containing the analyte is applied to the binding domains, the
analyte is bound to the binding domains. Antibodies (Ab), which are
suitable for selectively binding analyte (An) and have been labeled
with an ECL moiety (TAG) to form Ab-TAG, are then applied to the
analyte on the binding domains. After excess, unbound Ab-TAG is
washed off the binding domains, a potential waveform suitable for
triggering electrochemiluminescence is applied to the TAG by
electrodes (not shown) to trigger an ECL emission from any TAG on
the binding domains. The ECL signal is detected by light detection
means and recorded by digital computer means.
[0129] Further embodiments, features and variations of the
invention are provided as described hereinbelow.
5.1. Preparation of a Binding Surface
[0130] To better understand the invention, a more detailed
description of the preparation of binding domains on a support is
provided. A patterned array of binding domains on a surface that
are specific for a plurality of analytes is referred to herein as a
patterned, multi-array multi-specific surface or PMAMS. PMAMS are
prepared on a support, for example, by patterning of self-assembled
monolayers ("SAMs") (Ferguson et al, 1993, Macromolecules
26(22):5870-5875; Prime et al., 1991, Science 252:1164-1167;
Laibinis et al., 1989, Science 245:845-847; Kumar et al., 1984,
Langmuir 10(5):1498-1511; Bain et al., 1989, Angew. Chem.
101:522-528). Surface patterning methods also include the use of
physical etching (e.g., micromachining) (Abbott et al., 1992,
Science 257:1380-1382; Abbott, 1994, Chem. Mater. 6(5):596-602),
microlithography (Laibinis et al., 1989, Science 245:845-847),
attachment of chemical groups to the surface through the use of
photoactivatable chemistries (Sundberg et al., 1995, J. Am. Chem.
Soc. 117(49):12050-12057), and micro-stamping techniques (Kumar et
al., 1994, Langmuir 10(5):1498-1511; Kumar et al., 1993, Appl.
Phys. Lett. 63(14):2002-2004). Other surface patterning methods
include procedures for the spatially controlled dispensing of
fluids or particles (e.g., micropen deposition (e.g., using a
microfluidic guide to deliver onto a surface using X-Y
translation)), microcapillary filling (Kim et al., 1995, Nature
376:581), Ink-Jet technology, or syringe dispensers. Combinations
of these techniques may be used to provide complex surface
patterns. In FIG. 5A, a support 600 is shown with shape independent
binding domains that are represented, simply for illustration
purposes, as geometric shapes 602 to indicate that different
binding specificities may be present on a single support. Surface
604 between binding domains may be alternatively hydrophobic or
hydrophilic to confine deposition of binding reagent to form
binding domains. Binding domains and/or the surface(s) between
binding domains may be alternatively prone and resistant to
nonspecific binding, and/or they may be prone and resistant to the
attachment of binding reagents via covalent or non-covalent
interactions. In the case where non-specific binding through
hydrophobic interactions is not the desired method for attachment
of binding chemistries to the surface, detergent may be added to
prevent incidental non-specific binding from occurring.
[0131] The binding domains are broadly from 0.1 .mu.m to 10 mm in
width or diameter or widest dimension depending upon the geometry
of the domain. The surfaces are selectively derivatized to have
specific binding components exposed to e.g., the ECL assay
solution. Additionally, non-specific interactions at the binding
domains are decreased while maintaining a specific binding moiety
by incorporating moieties such as polyethyleneglycols on the
exposed surface of the discrete binding domains (Prime et al.,
1993, J. Chem Soc. 115:10714-10721; Prime et al., 1991 Science
252:1164-1167; Pale-Grosdemange et al., 1991, J. Am. Chem. Soc.
113:12-20).
[0132] The PMAMS may contain broadly from 2 to 10.sup.8 binding
domains. Preferably, the number of binding domains is from 50 to
500. In still other embodiments, the number of binding domains is
from 25 to 100. In still other embodiments, the number of binding
domain is from 2 to 20.
[0133] The support may be a variety of materials including but not
limited to glass, plastic, ceramic, polymeric materials,
elastomeric materials, metals, alloys, composite foils,
semiconductors, insulators, silicon and/or layered materials, etc.
Derivatized elastomeric supports can be prepared, e.g., as
described by Ferguson et al., 1993, Macromolecules 26:5870-5875;
Ferguson et al., 1991, Science 253:776-778; Chaudhury et al., 1992,
Science 255:1230-1232.
[0134] The surface of the support on which PMAMS are prepared may
contain various materials, e.g., meshes, felts, fibrous materials,
gels, solids (e.g., formed of metals) elastomers, etc. The support
surface may have a variety of structural, chemical and/or optical
properties. For example, the surface may be rigid or flexible, flat
or deformed, transparent, translucent, partially or fully
reflective or opaque and may have composite properties, regions
with different properties, and may be a composite of more than one
material. The surface may have patterned surface binding regions
and/or patterned regions where catalyses may occur according to the
invention on one or more surfaces, and/or an addressable array of
electrodes on one or more surfaces. The surfaces of the supports
may be configured in any suitable shapes including planar,
spheroidal, cuboidal, and cylindrical. In a specific embodiment,
the support bearing a PMAMS is a dipstick.
[0135] The support bearing a PMAMS may contain carbon, e.g.,
particulate carbon, graphite, glassy carbon, carbon black, or may
contain one or more carbon fibers. These fibers may be amorphous or
graphitic carbon.
[0136] A support bearing a PMAMS may contain "carbon fibrils",
"carbon nanotubes", "graphitic nanotubes", "graphitic fibrils",
"carbon tubules", "fibrils" and "buckeytubes", all of which terms
are used to describe a broad class of carbon materials (see
Dresselhaus, M. S.; Dresselhaus, G.; Eklund, P. C.; "Science of
Fullerenes and Carbon Nanotubes", Academic Press, San Diego,
Calif., 1996, and references cited therein). We use the terms
"fibrils" and "carbon fibrils" throughout this application to
include this broad class of carbon-based materials.
[0137] Individual carbon fibrils as disclosed in U.S. Pat. Nos.
4,663,230, 5,165,909, and 5,171, 560 are particularly advantageous.
They may have diameters that range from about 3.5 nm to 70 nm, and
length greater than 10.sup.2 times the diameter, an outer region of
multiple essentially continuous layers of ordered carbon atoms and
a distinct inner core region. Simply for illustrative purposes, a
typical diameter for a carbon fibril may be approximately between
about 7 and 25 nm, and a typical range of lengths may be 1 .mu.m to
10 .mu.m. Carbon fibrils may also have a single layer of carbon
atoms.
[0138] Carbon materials can be made to form aggregates. For
example, as disclosed in U.S. Pat. No. 5,110,693 and references
therein, two or more individual carbon fibrils may form microscopic
aggregates of entangled fibrils. These aggregates can have
dimensions ranging from 5 nm to several cm. Simply for illustrative
purposes, one type of microscopic aggregate ("cotton candy or CC")
resembles a spindle or rod of entangled fibers with a diameter that
may range from 5 nm to 20 .mu.m with a length that may range from
0.1 .mu.m to 1000 .mu.m. Again for illustrative purposes, another
type of microscopic aggregate of fibrils ("birds nest, or BN") can
be roughly spherical with a diameter that may range from 0.1 .mu.m
to 1000 .mu.m. Larger aggregates of each type (CC and/or BN) or
mixtures of each can be formed (vide infra).
[0139] Fibrils that can be used in a support include but are not
limited to individual fibrils, aggregates of one or more fibrils,
suspensions of one or more fibrils, dispersions of fibrils,
mixtures of fibrils with other materials (e.g., oils, paraffins,
waxes, polymers, gels, plastics, adhesives, epoxies, teflon,
metals, organic liquids, organic solids, inorganic solid, acids,
bases, ceramics, glasses, rubbers, elastomers, biological molecules
and media, etc.) as well as combinations thereof.
[0140] The fibrils may be magnetic in some cases and non-magnetic
in others. The extent to which fibrils can be made magnetic or
non-magnetic is controlled by the process used to produce the
fibrils. Examples of such process are disclosed in U.S. Pat. Nos.
4,663,230, 5,165,909, and 5,171,560. PMAMS are located on, in, or
in proximity to the supports described supra.
[0141] PMAMS can be generated from different types of surface
binding groups. Self-assembling monolayers that can be used to form
a monolayer on a surface to which they bind, include but are not
limited to alkane thiols (which bind gold and other metals),
alkyltrichlorosilane (e.g., which bind silicon/silicon dioxide),
alkane carboxylic acids (e.g., which bind aluminum oxides) as well
as combinations thereof. The monolayer may be formed first and then
linking chemistry used to attach binding reagents. Derivatization
after self-assembly produces a more perfect two-dimensional
crystalline packing of the monolayer on a support surface with
fewer pin holes or defects. The monolayer can be derivatized with
the binding reagents before or after self-assembly. Regular defects
in the monolayer may be desirable, and can be obtained by
derivatization prior to self-assembly of the monolayer or the
support surface. If the derivatized group (e.g., exposed binding
group) on the binding reagent is sterically large, it may create a
close-packed surface at the exposed end, but with regular gaps at
the metal surface. This is useful for allowing charge to flow
through these regular gaps to the ECL labeled moieties bound to the
portion contacting the sample solution.
[0142] The preparation of incomplete monolayers is known in the
art. Other procedures for the preparation of incomplete monolayers
include but are not limited to: the formation of monolayers from
dilute solutions of binding reagent, the termination of the
monolayer forming reaction before completion, the damaging of more
complete monolayers with radiation (e.g., ionic particles), light
or chemical reagents. In one embodiment, repeated stamping without
re-inking the stamp can give a range of defective monolayers
(Wilbur et al., 1995, Langmuir, 11:825)
[0143] PMAMS can be generated on the surface of matrices. Matrices
may be highly conducting, e.g., metal electrodes or conducting
polymer films; or matrices may be insulators; or semi-conducting
and/or of medium conductivity. The matrix material may be an ionic
conductor or a porous material. Such porous materials may be
utilized as support material and/or a conductive material and/or a
filter material and/or a channeling material (e.g., allowing
passage of fluids, ionic species etc.).
[0144] The porous material may be combined with additional
materials. For example, composite structures may be fabricated of
porous materials with additional porous materials, conductive
materials, semiconductive materials, channeling structures and/or
solutions (e.g., ionic fluids). Such composites may be laminar
structures, sandwich structures, and/or interspersed composites. A
solid matrix may be used which is a porous material supported on a
metal electrode. Alternatively, a porous material is sandwiched
between conducting materials, semiconducting materials or a
combination of semiconducting and conducting materials. One or more
binding domains may be contained on one continuous slab of the
porous material and/or may be located on a plurality of discrete
objects on the support each with one or more binding domains. The
porous material (e.g., gel) surface may be flat, hemispherical or
take on any regular or irregular shape and/or may have a variety of
physical properties (e.g., elastomeric, rigid, low density, high
density, gradient of densities, dry, wet etc.) and/or optical
properties (e.g., transparent, translucent, opaque, reflective,
refractive etc.) and or electrical properties (e.g. conductive,
semiconductive, insulating, variably conductive, for example wet
vs. dry etc.). The porous material may be a composite of more than
one materials.
[0145] A pattern of channels may be formed in the matrix. The
porous material layers may be from 5 microns to 2000 microns thick.
The porous material layers may also be thicker than 2 mm.
[0146] The pores may extend partially and/or fully through the
material or may be part of a network of pores. These pores may have
dimensions ranging broadly from 50 .ANG. to 10000 .mu.m. In a
preferred embodiment, the material has some pores with dimensions
ranging from 200 .ANG. to 500 .ANG. and some pores with dimensions
ranging from 0.5 .mu.m to 100 .mu.m.
[0147] The porosity of the material may be constant throughout the
material or may increase or decrease as a function of the position
in the material. The material may have a wide variety of pores of
different size distributed in a disorganized and/or random
manner.
[0148] For example, the material may have some pores that are large
enough to pass objects as large as biological cells, some pores
that can pass biological media as large as proteins or antibodies,
some pores that can pass only small (<1000 molecular weight)
organic molecules, and/or combinations thereof.
[0149] The porosity of the material may be such that one or more
molecules, liquids, solids, emulsions, suspensions, gases, gels
and/or dispersions can diffuse into, within and/or through the
material. The porosity of the material is such that biological
media can diffuse (actively or passively) or be forced by some
means into, within and/or through the material. Examples of
biological media include but are not limited to whole blood,
fractionated blood, plasma, serum, urine, solutions of proteins,
antibodies or fragments thereof, cells, subcellular particles,
viruses, nucleic acids, antigens, lipoproteins, liposaccharides,
lipids, glycoproteins, carbohydrates, peptides, hormones or
pharmacological agents. The porous material may have one or more
layers of different porosity such that biological media may pass
through one or more layers, but not through other layers.
[0150] The porous material may be able to support a current due to
the flow of ionic species. In a further refinement, the porous
material is a porous water-swollen gel, for example polyacrylamide
or agar. A variety of other gel compositions are available (for
example see Soane, D. S. Polymer Applications for Biotechnology;
Soane, D. S., Ed.; Simon & Schuster: Englewood Cliffs, N.J.,
1992 or Hydrogels in Medicine and Pharmacy, Vol. I-III; Peppas, N.
A. Ed.; CRC Press: Boca Raton, Fla., 1987). Binding domains can be
attached to matrices by covalent and non-covalent linkages. (Many
reviews and books on this subject have been written; some examples
are Tampion J. and Tampion M. D. Immobilized Cells: Principles and
Applications Cambridge University Press: NY, 1987; Solid Phase
Biochemistry: Analytical and Synthetic Aspects Scouten, W. H. Ed.,
John Wiley and Sons: NY, 1983; Methods in Enzymology, Immobilized
Enzymes and Cells, Pt. B Mosbach, K. Ed., Elsevier Applied Science:
London, 1988; Methods in Enzymology, Immobilized Enzymes and Cells,
Pt. C Mosbach, K. Ed., Elsevier Applied Science: London, 1987;
Methods in Enzymology, Immobilized Enzymes and Cells, Pt. C
Mosbach, K. Ed., Elsevier Applied Science: London, 1987; see also
Hydrogels in Medicine and Pharmacy, supra). For example, a protein
can be attached to a cross linked copolymer of polyacrylamide and
N-acryloylsuccinimide by treatment with a solution of the protein.
The binding domains may also be integrated into a porous matrix in
a step prior to polymerization or gelation. In one embodiment,
binding domains may be attached to uncrosslinked polymers by using
a variety of coupling chemistries. The polymers may then be
crosslinked (for example using chemistries which include amide
bonds, disulfides, nucleophilic attack on epoxides, etc.) (see for
example: Pollack et al., 1980, J. Am. Chem. Soc. 102(20):6324-36).
Binding domains may be attached to monomeric species which are then
incorporated into a polymer chain during polymerization (see
Adalsteinsson, O., 1979, J. Mol. Catal. 6(3): 199-225). In yet
another embodiment, binding domains may be incorporated into gels
by trapping of the binding domains in pores during
polymerization/gelation or by permeation of the binding domains
into the porous matrix and/or film. Additionally, binding domains
may be adsorbed onto the surface of porous matrices (e.g., polymer
gels and films) by nonspecific adsorption caused for example by
hydrophobic and/or ionic interactions. Biotin may be advantageously
used as a linking or binding agent. Avidin, streptavidin or other
biotin binding agents may be incorporated into binding domains.
[0151] PMAMS can be generated on porous materials (e.g., gels) with
varying pore size and solvent content. For example, polyacrylamide
gels varying in pore size can be made by varying the concentration
of acrylamide and the degree of crosslinking.
[0152] On such PMAMS with pore sizes smaller than the analyte,
binding reactions will occur substantially on the surface of the
gel. In this case, filtration and/or electrophoresis through the
gel can be used to concentrate analytes at the surface of the gel
and modulate the kinetics (e.g., increase the rate) of the binding
reaction. Faster kinetics is advantageous in rapid assays (e.g.,
short times to results) and may generate increased sensitivity in a
shorter time period.
[0153] On PMAMS with pore sizes larger than the analyte, binding
reactions can occur on the surface as well as in the bulk of the
gel. In this case, filtration can be used and/or electrophoresis
can be used to increase the kinetics of binding and remove unbound
species from the surface.
[0154] PMAMS formed on gels can be stored wet and/or they may be
stored in a dried state and reconstituted during the assay. The
reagents necessary for ECL assays can be incorporated in the gel
before storage (by permeation into the gel or by incorporation
during formation of the gel) and/or they can be added during the
assay.
[0155] Patterned binding domains of a PMAMS can be generated by
application of drops or microdrops containing each binding domain
in the matrix in a liquid form to a substrate. Solidification
and/or gelling of the liquid can then be caused by a variety of
well known techniques (polymerization, crosslinking, cooling below
the gelling transition, heat). Agents that cause solidification or
gelation may be included in the drops, so that at some time after
dispensing, the drops solidify and/or gel. A subsequent treatment
(e.g., exposure to light, radiation and/or redox potential) may be
used to cause solidification and/or gelation. In other embodiments
such drops or microdrops may be slurries, pre-polymeric mixtures,
particulate groups, and/or substantially solid drops. Additionally
vapor phase deposition may be utilized.
[0156] Patterning can also be achieved by forming a layered
structure of matrices each containing one or more binding domains.
For example, agarose linked (by standard chemistries) to an
antibody could be poured into a container and allowed to gel by
cooling. Subsequent layers containing other antibodies could then
be subsequently poured on the first layer and allowed to gel. The
cross section of this layered structure gives a continuous surface
presenting a plurality of distinct binding domains. Such cross
sections may be stacked and another cross section may be cut to
create a PMAMS surface with even greater density of binding
domains. Alternatively, lines of a matrix containing a given
binding element are laid down adjacent to one another and/or
stacked. Such structures may also be cut in cross-section and
utilized as a PMAMS surface.
[0157] Patterning can also be achieved by taking advantage of the
ability of some matrices to achieve separation. For example, a
mixture of nucleic acid probes could be separated by
electrophoresis in a polyacrylamide slab generating a surface
presenting a plurality of distinct binding domains.
[0158] Microfluidics guides may also be used to prepare the PMAMS
binding domains on a support. A partial list of microfluidic guides
includes hollow capillaries, capillaries made of and/or filled with
a matrix (e.g., a porous or solvent swollen medium), solid supports
which can support a thin film or drop of liquid. The capillary may
be solid and reagents flow along the outside surface of the
capillary, a reagent fluid reservoir may be exposed to a porous
matrix tip which is brought into contact with a PMAMS surface. For
example, the reagent reservoir may be continuously or periodically
refilled so that a given porous matrix tip may reproducibly deposit
reagents (e.g., alkane thiols to form monolayers and/or binding
reagents etc.) a plurality of times. Additionally, varying the
porosity of the tip can be utilized to control reagent flow to the
surface. Different or identical binding reagents may be present in
a plurality of capillaries and/or multiple distinct binding agents
may be present in a given capillary. The capillaries are brought
into contact with the PMAMS (e.g., patterned SAM) surface so that
certain regions are exposed to the binding reagents so as to create
discrete binding domains. Different binding reagents, each present
in a different microfluidic guide are delivered concurrently from
the fluidic guide array onto a metal surface, SAM, etc, as desired.
Microfluidic guides can also be used to ink a microstamp with a
desired molecule prior to application to the support surface. For
example, individual microfluidic guides can be used to apply
different binding reagents linked to a moiety that promotes
adsorption to the surface of the support (e.g., a free thiol on a
hydrocarbon linker, which promotes adsorption to gold), to form a
PMAMS. Thus, for example, a microstamp inked via the use of
microfluidic guides with antibodies of different specificities that
have incorporated a linker with a free thiol, can be used to apply
such antibodies in desired areas on a gold surface to form discrete
binding domains of a PMAMS.
[0159] Microfluidic guide also refers to microprinting devices
which deliver microdrops of fluid by ejection of the drop through a
small orifice (e.g., an Ink-Jet printer). The ejection drops in
these devices may be caused by different mechanisms including
heating, electrostatic charge, and/or pressure from a piezo device.
Patterning of more than one liquid can be achieved through the use
of multiple orifices and/or one orifice and appropriate
valving.
[0160] In one method for preparation of a PMAMS, microfluidic
guides are used to deliver (preferably concurrently) directly onto
discrete regions on a surface, drops containing the desired binding
reagents, to form discrete binding domains. The binding reagents
may contain a functional chemical group that forms a bond with a
chemical group on the surface to which it is applied. In another
variation, binding reagents in the drop are nonspecifically
adsorbed or bound to the surface (e.g., dried on the surface).
[0161] Alternatively, drop(s) deposited on a surface contain
reagents that can form a matrix. This matrix may be a solid,
polymer or a gel. The formation of the matrix may be by evaporation
of solvent. It may be by polymerization of monomeric species. It
may be by cross-linking of preformed polymers. It may be by
modulating temperature (e.g., cooling and/or heating). It may be by
other methods. For example, a polymeric species may be cooled
through a cooling transition or by addition of a reagent that
causes gelling. The formation of the solid matrix may be induced by
generation of reactive species at an electrode (including the
substrate), by light (or other radiation) by addition of reagents
that induce solidification or gelling, by cooling or heating.
Additionally, the surface may contain catalysts capable of
initiating matrix formation (e.g. gelling or polymerization).
[0162] In a preferred technique, patterned hydrophilic/hydrophobic
regions to prevent spreading of applied fluids or gels can be used.
Such a fluid or gel may contain binding reagents to be linked to a
surface on a support to form a binding domain of the PMAMS. In this
case, use of such a hydrophilic/hydrophobic border aids in
confining the produced binding domain to a discrete area.
Alternatively, the fluid contains reagents which can form a matrix
on the surface and binding reagents are contained within a defined
region when deposited on a surface. For example,
hydrophilic/hydrophobic border aids may be utilized to confine the
drop to a defined region. Additionally, either the hydrophilic or
hydrophobic areas may present groups which can be incorporated
(e.g., covalently or non-covalently bound) into the matrix,
allowing for a more stable adhesion of the matrix to the substrate
(Itaya and Bard, 1978, Anal. Chem. 50(11):1487-1489). In another
technique, the fluid or gel that is applied is the sample
containing the analyte of interest, and the sample is applied to a
prepared PMAMS. In one preferred example, capillaries containing
hydrophilic solutions can be used to deposit a solution onto
discrete areas, creating hydrophilic domains surrounded by
hydrophobic regions. Alternatively, hydrophobic binding domains
surrounded by hydrophilic regions can be used with a hydrophobic
fluid containing binding reagents or analyte(s)). Hydrophobic and
hydrophilic are relative terms, with respect to each other and/or
with respect to the sample to be applied, i.e., such that the
spread or wetting of a fluid or gel sample applied to the binding
domains is controlled. Further, controlled solution deposition from
the microfluidics array may be accomplished using physical surface
features (e.g., wells or channels on the surface). A microfluidics
guide can be included in a cassette, or more preferably, used to
apply specific reagents to a support prior to use.
[0163] More than one linking chemistry may be applied to the same
support surface and/or a surface with both hydrophilic and
hydrophobic binding domains can be created using multiple stamps.
For example, an area where a hydrophilic binding domain is desired
at position 1 and a hydrophobic binding domain is desired at
position 2 can be prepared as follows. A first hydrophilic stamp is
made which has a disk at position 1 and a larger ring at position
2. A second hydrophobic stamp is made with a disk at position 2
which fits inside the ring monolayer left by stamp 1. Finally, the
surface is washed with a hydrophobic solution of monolayer
components.
[0164] In particular, a PMAMS is generated by micro-contact
printing, i.e., stamping. The monolayer so applied is composed of a
surface-binding group, e.g., for a gold surface, a thiol group with
an alkane (e.g., (CH.sub.2).sub.n)) spacer is preferred. A spacer
group is linked (preferably covalently bound) to a linking group A.
"A" can be, e.g., avidin, streptavidin or biotin or any other
suitable binding reagent with an available complementary binding
partner "B". The A:B linkage may be covalent or non-covalent and
some linkage chemistries known to the art that can be used are
disclosed by, e.g., Bard et al. (U.S. Pat. Nos. 5,221,605 and
5,310,687). "B" is further linked to a binding reagent such as an
antibody, antigen, nucleic acid, pharmaceutical or other suitable
substance for forming a binding domain that can bind to one or more
analytes of interest in a sample to be tested. B may also be linked
to an ECL TAG or label. Linking group B may be delivered to the SAM
by means of a capillary or microfluidics guide array (FIGS. 5A-5C)
able to place a plurality of "B" reagents with different binding
surface specificities on the monolayer "A" linkage. A and B can
also be linked before or prior to being attached to the monolayer.
As discussed, in FIG. 5A, shape independent binding domains are
represented, simply for illustration purposes as geometric shapes
602 to indicate that different binding specificities may be present
on a single support 600. FIG. 5B provides a top view of a
microfluidic guide (e.g., capillary) array 606. The dots 610 are
the guides in cross section. FIG. 5C provides a side view of a
microfluidic guide array 608. The lines emerging from the top and
bottom are individual microfluidic guides 610. The geometric shapes
612 on the lower aspect represent specific binding domains formed
upon delivery of binding reagent from each individual
capillary.
[0165] By way of example, after the first stamping discussed supra,
the bare surface (e.g., gold) regions may be reacted with a second
alkane thiol which does not have linking chemistry A and is of the
opposite hydrophobicity/hydrophilicity of the first monolayer
above. In this way, specific linking domains are prepared on a
surface.
[0166] A binding reagent that is specific or for one analyte of
interest may be used for each binding domain or a binding reagent
may be used that specifically binds to multiple analytes of
interest.
[0167] In yet another variation, a support surface may be stamped
multiple times by materials (e.g., binding reagents, ECL labels,
SAMs) having different linking chemistries and/or binding moieties
as shown by FIG. 5A above.
[0168] The binding reagents that are patterned can be stable and/or
robust chemical groups (e.g., that survive the conditions to which
they are subjected) which are later linked to less stable or robust
binding groups. Multiple binding linkages may be utilized so as to
optimize the conditions of each step in the preparation of a PMAMS
surface and/or simplify the manufacturing of PMAMS surfaces. For
example, a first PMAMS surface may be fabricated in a generic
fashion and then modified to create different PMAMS surfaces. In
another example, a generic PMAMS surface may be reacted with a
solution mixture of binding reagents which themselves contain
binding domains which direct them to particular regions (e.g.,
binding domains) on the PMAMS surface. For example, a pattern of
binding domains each presenting a different oligo(nucleotide)
sequence is linked to the surface. This surface is then treated
with a solution containing a mixture of secondary binding reagents,
each linked to a oligo (nucleotide) sequence complementary to a
sequence on the surface. In this way, patterning of these secondary
binding elements can be achieved. Preferably, the oligo
(nucleotide) sequences are 6-30 mers of DNA. Certain sets of 6-30
mer sequences may contain substantially similar sequence
complementarity so that the approximate binding constants for
hybridization are similar within a given set and discernably
different from less complementary sequences. In another embodiment,
the secondary binding elements are proteins (for example,
antibodies).
[0169] Methods described to inhibit wetting or spread of applied
reagents or sample on a surface as described in Section 5.13 infra,
can also be used in the preparation of PMAMS (and/or in sample
application). Applied potential (e.g., from the
electrode/counterelectrode pair) may be used to further control the
deposition and/or spreading of reagents and/or samples (see, e.g.,
Abbott et al., 1994, Langmuir 10(5):1493-1497).
[0170] The PMAMS binding reagents may be located on materials that
contain carbon, e.g. particulate carbon, carbon black, carbon
felts, glassy carbon and/or graphitic carbon. In some embodiments,
they may be located on carbon fibers, e.g. carbon fiber, or carbon
fibrils. The binding reagents may be located on individual carbon
fibrils or they may be located on aggregates of one or more
fibrils. In many embodiments, the PMAMS binding reagents may be
located on suspensions or dispersion of these carbon materials,
mixtures of carbon materials with other materials as well as
combinations thereof.
[0171] The PMAMS binding reagents may be located on a plurality of
individual fibrils and/or aggregates of fibrils localized on or in
or in proximity to a support. In one example, the binding reagents
are localized on dispersed individual fibrils or fibril aggregates.
These fibrils or aggregates of fibrils may be localized spatially
into distinct domains on a support, and may constitute binding
domains. In another example, the binding reagents may be located on
aggregates of carbon particles.
[0172] In another example, individual such binding domains or a
plurality of such binding domains are located in spatially distinct
regions of the support. By way of a non-limiting example,
individual such binding domains or collections of binding domains
may be located in depressions, pits and/or holes in the support. In
still another example, individual binding domains or a plurality of
domains may be located in drops of water, gels, elastomers,
plastics, oils, etc. that are localized on the surface of the
support. In yet another example, individual binding domains may be
localized on the support by a coating (which may be patterned) that
has different binding affinities for different binding reagents
and/or binding reagent/fibril ensembles.
[0173] Binding domains located on a plurality of individual fibrils
and/or aggregates of fibrils may be prepared on a support by means
of one or more microfluidic guides (e.g., a capillary). Different
or identical binding reagents may be present in or on a plurality
of microfluidic guides and/or multiple distinct binding agents may
be present in or on a given microfluidic guide. The capillaries may
be brought into contact with the support (spotting) and/or may
deliver the reagents while either the microfluidic guide and/or the
surface is being scanned or translated relative to the other (i.e.,
a penlike method of writing). The microfluidic guide may deliver
the binding reagents located on the fibrils to the support so that
certain regions of the support are exposed to the fibril-binding
reagent complex(es) so as to create a discrete binding domain(s).
In a preferred aspect, different binding reagents, each present in
a different microfluidic guide are delivered concurrently from the
guide array onto the support. In one example, binding reagents
and/or the fibrils on which they are localized are derivatized with
a chemical functional group that forms a bond (e.g., covalent or
non-covalent interaction) to the surface of the support. In some
embodiments, the binding reagents and fibrils are non-specifically
bound or adsorbed to the surface. In yet another aspect, the
binding reagents localized on the fibrils may be delivered to
depressions, pits and/or holes in the surface of the support. In
another example, the binding reagents are delivered to a surface
that is coated with a material that has a stronger or weaker
binding affinity for certain binding reagents or binding
reagent/fibril ensembles and so creates domains of the reagents
that are localized spatially and distinctly from other binding
reagents
[0174] The binding reagents are localized on one or more individual
fibrils or aggregates of fibrils that are magnetic. In such a case,
a magnetic support may attract the binding reagents localized on
magnetic fibrils to the support.
[0175] The support may contain several distinct regions that are
magnetic and are surrounded by regions that are not magnetic.
Binding reagents localized on magnetic fibrils may be localized on
magnetic regions of the support. In one example, the support may
contain one or more distinct regions that are magnetic and are
surrounded by regions that are not magnetic, and the strength of
the magnetic field in the magnetic regions can be modulated or
switched. In this aspect, use of such a modulated or switchable
magnetic field aids in affixing or releasing the binding reagents
localized on fibrils from the surface of the support and so may
serve to stir or mix said domains.
[0176] There are broadly from 2 to 10.sup.8 binding domains and
preferably from 25 to 500 domains.
[0177] The binding domains may be located on the working electrode
and/or the counter electrode.
[0178] The different embodiments described herein for different
types of PMAMS, supports, and electrodes and configurations thereof
may also be practiced in combination with each other.
[0179] The PMAMS supports may be preserved (e.g., through
protective surface coatings, drying the surface, robust packaging
under vacuum or inert atmosphere, refrigeration and related
methods) for later use.
5.2. Binding Reagents
[0180] The binding domains of the invention are prepared so as to
contain binding reagents that specifically bind to at least one
analyte (ligand) of interest. Binding reagents in discrete binding
domains are selected so that the binding domains have the desired
binding specificity. Binding reagents may be selected from among
any molecules known in the art to be capable of, or putatively
capable of, specifically binding an analyte of interest. The
analyte of interest may be selected from among those described in
Section 5.10 infra, "ECL Assays That May Be Conducted." Thus, the
binding reagents include but are not limited to receptors, ligands
for receptors, antibodies or binding portions thereof (e.g., Fab,
(Fab)'.sub.2), proteins or fragments thereof, nucleic acids,
oligonucleotides, glycoproteins, polysaccharides, antigens,
epitopes, cells and cellular components, subcellular particles,
carbohydrate moieties, enzymes, enzyme substrates, lectins, protein
A, protein G, organic compounds, organometallic compounds, viruses,
prions, viroids, lipids, fatty acids, lipopolysaccharides,
peptides, cellular metabolites, hormones, pharmacological agents,
tranquilizers, barbiturates, alkaloids, steroids, vitamins, amino
acids, sugars, nonbiological polymers, biotin, avidin,
streptavidin, organic linking compounds such as polymer resins,
lipoproteins, cytokines, lymphokines, hormones, synthetic polymers,
organic and inorganic molecules, etc. Nucleic acids and
oligonucleotides can refer to DNA, RNA and/or oligonucleotide
analogues including but not limited to: oligonucleotides containing
modified bases or modified sugars, oligonucleotides containing
backbone chemistries other than phosphodiester linkages (see, for
example, Nielsen, P. E. (1995) Annu Rev. Biophys. Biomcl. Street.
24 167-183), and/or oligonucleotides, that have been synthesized or
modified to present chemical groups that can be used to form
attachments to (covalent or non-covalent) to other molecules (where
we define a nucleic acid or oligo(nucleotide) as containing two or
more nucleic acid bases and/or derivatives of nucleic acid
bases).
[0181] The PMAMS of the invention may have a plurality of discrete
binding domains that comprises at least one binding domain that
contains binding reagents that are identical to each other and that
differ in specificity from the binding reagents contained within
other binding domains, to provide for binding of different analytes
of interest by different binding domains. By way of example, such a
PMAMS comprises a binding domain containing antibody to thyroid
stimulating hormone (TSH), a binding domain containing an
oligonucleotide that hybridizes to hepatitis C virus (HCV), a
binding domain containing an oligonucleotide that hybridizes to
HIV, a binding domain containing an antibody to an HIV protein or
glycoprotein, a binding domain that contains antibody to prostate
specific antigen (PSA), and a binding domain that contains antibody
to hepatitis B virus (HBV), or any subset of the foregoing.
[0182] A PMAMS may have a plurality of binding domains that
comprises at least one binding domain that contains within it
binding reagents that differ in binding specificity, so that a
single binding domain can bind multiple analytes of interest. By
way of example, such a PMAMS comprises a binding domain that
contains both antibody to a T cell antigen receptor and antibody to
a T cell surface antigen such as CD4.
[0183] A PMAMS may have a plurality of binding domains that
comprises (i) at least one binding domain that contains binding
reagents that are identical to each other and that differ in
specificity from at least one of the binding reagents contained
within the other binding domains; and (ii) at least one binding
domain that contains within it binding reagents that differ in
binding specificities. By way of example, a PMAMS is made that has
(a) at least one binding domain that contains binding reagents of a
single identity, e.g., antibody to a T cell antigen receptor, e.g.,
.alpha., .beta. T cell antigen receptor or .gamma., .delta. T cell
antigen receptor), thus allowing this at least one binding domain
to bind all cells expressing this T cell antigen receptor; and (b)
at least one binding domain that contains two different binding
reagents, e.g., antibody to T cell antigen receptor and antibody to
CD4, thus allowing this at least one binding domain to bind
CD4.sup.+ T lymphocytes expressing that T cell antigen receptor
(i.e., a subpopulation of T lymphocytes).
[0184] In another embodiment, at least one binding domain contains
binding reagents which are different molecules but which have the
same binding specificities (e.g., binding reagents such as
epidermal growth factor and antibody to the epidermal growth factor
receptor).
[0185] A plurality of binding reagents can be chosen so that even
though the binding reagents are different and have different
binding specificities, they recognize the same analyte (in an
alternative embodiment, different analytes are recognized). For
example, where the analyte is an analyte that has numerous binding
moieties (e.g., a cell, which has different cell surface antigens),
different binding reagents that bind to different binding moieties
will recognize the same analyte. As another example, antibodies to
different cell surface antigens on a single cell will recognize the
same cell. As yet another example, antibodies to different epitopes
of a single antigen can be used as binding reagents to recognize
the antigen.
[0186] A plurality of binding reagents can be chosen so that a
plurality of binding domains may be formed where such binding
domains recognize the same analyte but with different affinities.
The use of such a PMAMs allows for the detection of an analyte over
a greater range of concentrations (e.g., a high affinity binding
domain may be saturated with analyte under conditions that do not
saturate a lower affinity binding domain).
[0187] In still a further embodiment, only binding reagent(s) that
specifically bind a single analyte of interest are present in one
or more binding domains. Alternatively, binding reagents that
specifically bind more than one analyte of interest are present in
one or more binding domains (e.g., a cross-reactive antibody). In a
particular design, binding reagents can be used that bind a class
of analytes, e.g., with similar characteristics.
[0188] Binding domains may also be incorporated into a PMAMS that
contain binding reagents that are specific for a desired standard
analyte and that are utilized as an internal standard (e.g., a
binding domain which can be contacted with a sample containing a
defined quantity of an analyte to which the binding reagents bind).
Multiple binding domains containing binding reagents specific for
the same analyte(s) can also be incorporated into a PMAMS so as to
allow statistical averaging of analytical results. The binding
reagents may not only be specific for the same analyte, but may be
identical, thus recognizing the same binding moiety on the analyte.
Thus, a plurality of binding domains (e.g., within a range of 2 to
10.sup.8) can be prepared that specifically bind to the same
binding moiety, so that the ECL readings can be statistically
averaged to control for variation and improve accuracy. The
plurality of binding domains on a PMAMS may be specific for a
control analyte or an analyte of interest, or both, on a single
support.
[0189] As another example, one or more discrete binding domains may
be prepared with a known initial concentration number of ECL
labels. The built-in ECL layer serves as a control to monitor,
e.g., label degradation and temperature effects.
[0190] A binding reagent may be used that is an enzyme specific for
a substrate (said substrate being the analyte of interest), in
which a product of the enzymatic reaction upon the substrate is a
reporter agent (an agent that is detectable), e.g., a product that
triggers an ECL reaction, a fluorescent molecule, a substance that
changes color upon contact with appropriate enzyme (e.g., a
chromogenic substrate for horseradish peroxidase), etc. In an
example of such an embodiment, the enzyme used as a binding reagent
is glucose dehydrogenase (GDH), which can be used to detect or
measure glucose in a sample. An ECL label is situated within or
near to the binding domain containing the GDH. NADH is produced by
the action of the enzyme upon glucose, NADH being capable of
reacting with the ECL labels to promote ECL (Martin et al., 1993,
Anal. Chim. Acta 281:475).
[0191] Binding domains containing binding reagents which increase
background binding (i.e., that bind to a binding moiety present on
the analyte of interest as well as on other analytes in the sample)
can be used to increase signal to noise ratios during the detection
or measurement of electrochemiluminescence. By way of example,
where the analyte of interest is a specific cellular subpopulation
(e.g., CD4.sup.+ cells) and the sample is a fluid sample (e.g.,
blood) that contains cells from a patient, antibody to sialic acid
can be used as a binding reagent to increase background binding to
virtually all cells in the sample (since sialic acid is a component
of virtually all cell surface glycoproteins), and an antibody to a
cell surface antigen specific to the cellular subpopulation (e.g.,
antibody to CD4) can then be used as a binding reagent (in the same
or different binding domain as that containing the antibody to
sialic acid).
5.3. Voltage Waveform
[0192] The voltage waveform (change in electrical potential/time)
impressed upon the electrodes and counter-electrodes of ECL cells
must be sufficient to trigger an ECL reaction. This voltage
waveform usually is in the form of a uniform voltage sweep starting
at a first voltage, moving steadily to a second voltage, moving
back through the first voltage to a third voltage and then back
again to the first voltage. For example, the waveform may start at
a first voltage in a range from -0.5 through 0.5 volts, up to a
second voltage in a range from 1 through 2.5 volts and moving back
through the first voltage to a third voltage ranging from 0.0 to -1
volts. As another example, in simpler waves, the voltage can be
modified from 0.0 to +3.5 to 0.0. The voltage waveforms may
incorporate linear ramps, step functions, and/or other functions.
The voltage waveforms may incorporate periods of time when the
voltage remains fixed at one potential. The applied potential may
be controlled relative to one or more reference electrodes, or, no
reference electrodes may be used. Additionally, negative potential
may be used. Thus, the voltages used to induce ECL emissions from
the cassette of the present invention will be readily selected for
optimal ECL signal intensity and specificity for the ECL label and
assay medium.
[0193] In some applications, the voltage is preferably varied as
the light emitted from the binding domain is measured. This is
particularly important to determine the threshold value of the
electrical field necessary to cause the binding domain to emit
light. In this case, the electrical potential applied at the
binding domain starts at a value believed to be below the threshold
required to emit light, and a first measurement is made of the
light emitted. If no light is measured, or the light is below a
predetermined threshold, the electrical potential applied across
the electrode pair is increased under computer control, such as by
a computer controlled voltage source and another light measurement
is made. This process can be repeated until the predetermined
appropriate amount of light is received. In this way, the voltage
applied may be used as the assay signal.
[0194] The voltage waveform may contain an AC component. The use of
such a waveform allows for better signal to noise in the detection
of the ECL signal, e.g., by filtering out signals that differ in
frequency from the voltage input).
[0195] The ordinary artisan who is familiar with the voltage and
current settings as disclosed, for example, by U.S. Pat. Nos.
5,324,457 and 5,068,088 will readily be able to select the optimum
operating voltages and voltage sweep for triggering ECL
emission.
[0196] The potential required for generating ECL may be generated
by illumination of the working electrode surface if the working
electrode is a semiconductor or contains another moiety that
generates electrical current in response to light.
5.4. Addressable Electrodes and Methods for Using the Same
[0197] Numerous methods may be used for addressing the plurality of
electrode/counterelectrode pairs. Several illustrative such
techniques are illustrated in FIGS. 14-18. Shown in those figures
by way of example are four electrode/counterelectrode pairs 101,
102, 103, 104 and a waveform generator which typically is a digital
computer and which preferably is the same computer used for
processing the ECL detected by the detection means.
[0198] In FIG. 14, each electrode/counterelectrode pair 101-104 is
individually addressed by a pair of lines connected to the waveform
generator. By way of example, lines 105, 106 access
electrode/counterelectrode pair 101. An appropriate waveform may be
applied by the waveform generator at any given time to any one or
more of the pairs of lines connected to the various
electrode/counterelectrode pairs.
[0199] To reduce the number of connections required to address the
electrode pairs, alternatives to the direct connection scheme of
FIG. 14 are provided. For example, a row-and-column accessing
scheme is illustrated in FIG. 15 for electrically energizing some
or all of the electrodes. In this scheme, one of the electrodes
201, 202 in each column of the plurality of
electrode/counterelectrode pairs is connected to a common
electrical conductor 205 on support 200, and each of the
counterelectrodes in each row of the plurality of
electrode/counterelectrode pairs is connected to conductor 207, 208
on the support 200. Conductors 205, 206 connect to connections C1,
C2, respectively, at the edge of support 200 and conductors 207,
208 connect to connections R1, R2, respectively. Each of these
connections is then connected by a separate line to the waveform
generator. As a result, in the configuration of FIG. 15, the number
of required connections and signal lines from the waveform
generator has been reduced from 8 to 4.
[0200] To enable rapid and sequential energizing of each electrode
pair, a computer controlled switching device is beneficial. The
configuration of FIG. 16 shows a plurality of electrodes connected
to a first multiplexer 310. A plurality of counterelectrodes are
connected to a second multiplexer 320. The first multiplexer is
also connected to a first pole of a voltage source 330 that
typically supplies the time varying electrical potential described
infra. The second multiplexer is also connected to a second pole of
the voltage source. Using addressing lines A0-A3 electrically
connected to each of the multiplexers and connected to latch 340, a
computer processor 350 can direct the multiplexers to selectively
connect any or all of the first electrodes to the first pole of the
voltage source, and any or all of the second electrodes to the
second pole of the voltage source.
[0201] As shown in FIG. 17, a plurality of voltage sources are
connected through separate sets of multiplexers to each of the
electrodes. If a first electrical potential or range of electrical
potentials is required at a particular electrode pair, the
multiplexers 410, 420 associated with the voltage source 430
providing that potential are addressed by the computer processor
350, typically through a latch 340, thereby connecting that
particular voltage source to the electrode pair in question. If a
different electrical potential or range of electrical potentials is
required for another electrode pair, the multiplexers 440, 450
associated with that different voltage source 460 are addressed by
the computer processor, thereby connecting that voltage source
through the associated multiplexers 440, 450 to the electrode
pair.
[0202] If the electrode array in this embodiment has at least a
portion of the electrode pairs independently driveable, as shown in
FIG. 14, or 15, for example, one electrode pair can be driven by
one voltage source while another electrode pair is simultaneously
driven with another voltage source. Alternatively, the two voltage
sources of FIG. 17 can be replaced with a single voltage source
connected to both sets of multiplexers in parallel, allowing two
electrode pairs to be driven from the same voltage source.
[0203] Instead of a duplicate set of multiplexers for each voltage
source as shown in FIG. 17, a plurality of voltage sources 520, 530
can be provided as shown in FIG. 18. These voltage sources can be
connected through a computer controlled electrical switch 510 or
switches to a single set of multiplexers 310, 320. As shown in FIG.
18, the computer would direct switch 510 to connect a particular
voltage source to the multiplexers, and would also direct the
multiplexers (by signalling their address lines A0-A3) to connect
the selected voltage source to the particular electrode pair
desired.
[0204] Alternatively, the electrical potential applied to each of
the electrode pairs in any embodiment can be varied. This is of
particular benefit when a cassette having a plurality of different
binding domains is used. Such a cassette may require a different
range of applied electrical potential at different binding domains.
Several different embodiments capable of varying the electrical
potential applied to each electrode are contemplated.
[0205] Advantageously, a computer controlled voltage source may be
used. A computer controlled voltage source is one that can be
addressed by a computer to select a particular electrical potential
to be supplied. Alternatively it can be programmed to sequentially
apply a particular range of electrical potentials over a
predetermined time. In such a system, address lines electrically
connected to the computer and the voltage source would allow the
computer to program the voltage source to produce the particular
electrical potential to be applied to the electrode pair to be
energized.
[0206] Additional methods for addressing the plurality of electrode
pairs may also be used. For example, a plurality of reference
electrodes may be placed in proximity to each of the plurality of
electrode and counterelectrode pairs in order to sense the voltage
applied thereto. In this way, additional control of the voltage
waveform may be maintained.
[0207] FIG. 36 shows another embodiment of the invention; arrays of
electrodes (3600, 3601) are supported on each of two surfaces
(3602, 3603) separated by a pattern of gaps in an insulator 3604
(for example a plastic sheet with punched holes 3605. Each
electrode may pass over a plurality of gaps. If a potential is
applied between one electrode on each surface, current can only
pass through a gap contacting both electrodes, thus limiting the
location of any electrochemistry or ECL which may occur. In the
preferred embodiment shown in the figure, the electrodes (3600,
3601) are arrays of lines on a support. The two sets of electrodes
on the two surfaces are oriented perpendicular to each other. Gaps
in the insulating sheet are located only at the intersection of the
electrodes from each surface.
[0208] This embodiment has the advantage over individually
addressed electrode pairs that less electrical leads are
required.
[0209] In an alternate embodiment, the insulator 3604 is omitted
and the surfaces are placed in close proximity so that only a
narrow gap exists between the two surfaces. In this embodiment, a
potential applied between are electrode on each surface will
preferentially cause current to pass at the intersection of the
electrode (i.e., where the distance between the electrodes is
minimal) thus limiting the location of any electrochemistry or ECL
which may occur.
5.5. Light Detection
[0210] The light generated by the triggered ECL emission is
detected by an appropriate light detector or detectors positioned
adjacent to the apparatus of the invention. The light detector may
be, for example, film, a photomultiplier tube, photodiode,
avalanche photo diode, charge coupled device ("CCD") or other light
detector or camera. The light detector may be a single detector to
detect sequential emissions or may be plural to detect and
spatially resolve simultaneous emissions at single or multiple
wavelengths of emitted light. The light emitted and detected may be
visible light or may be emitted as non-visible radiation such as
infrared or ultraviolet radiation. The detector or detectors may be
stationary or movable. The emitted light or other radiation may be
conducted to the detector or detectors by means of lenses, mirrors
and fiberoptic light guides or light conduits (single, multiple,
fixed, or moveable) positioned on or adjacent to the binding
surface of the cassette or the detector may receive the light
directly. In addition, the supports, PMAMS and electrode surfaces
themselves can be utilized to guide or allow transmission of
light.
[0211] The PMAMS may be formed on the surface of an array of light
detectors so that each detector only receives light from one
binding domain. The array of light detectors may be a CCD chip, and
the binding domains may be attached (using standard coupling
chemistries) to the surface of the semiconductor device.
[0212] Drops deposited on the binding domains, or on a near, second
surface, can be used as microlenses to direct or control emitted
light. Alternatively, a light detector can be oriented directly in
front of the cassette; and various light focusing devices, such as
parabolic reflectors or lenses may be employed instead of a light
conduit to direct light from any of a plurality of binding domains
to the detector. The light emitted from at least two discrete
binding domains may be measured simultaneously or sequentially.
[0213] Error due to thermal drift, aging of the apparatus, or the
electrical noise inherent in light detectors may be controlled by a
"chopper" means between the light measuring device and the binding
domain being measured. The chopper can be any one of the common
mechanical choppers well known to those of ordinary skill in the
art, such as a spinning disk with slots or cutouts that allow light
to pass. Alternatively, the light can be chopped by an LCD shutter,
an array of LCD shutters, a solid state light valve or valves or
the like. Alternatively, a planar array of LCD shutters or
solid-state light valves such as those known in the art of optical
computing may be used. These devices are preferably located between
the plane of the cassette, and the light conduit (or conduits) or
light focusing devices that direct light from the binding domains
to the light detector. In an embodiment, a shutter is located above
each of the binding domains. When using an LCD shutter or light
valve, the shutters may be modulated at different frequencies to
simultaneously provide different chopping rates for different light
emitting binding domains. Using this technique, a plurality of
different light signals may be superimposed and simultaneously
measured by a single detector. An electronic band pass filter
electrically connected to the light detector may then be used to
separate the electrical single signal into several electrical
components, each corresponding to one of the plurality of
individual light components. By chopping the light, as above, or
using other mechanism well known to the art, an AC light waveform
is created that allows the DC noise component to be electronically
filtered out.
[0214] Also, the ECL signal may be calibrated by comparison to
results previously determined with standard reagents to correct for
signal modulation due to reagent depletion.
5.6. Analysis of ECL signals
[0215] Signals arising from a given binding domain can have a range
of values, and these values correlate with quantitative measurement
to provide an `analog` signal. In another technique a `digital`
signal is obtained from each domain to indicate that an analyte is
either present or not present.
[0216] Statistical analysis is used for both techniques, and is
particularly useful for translating a plurality of digital signals
so as to provide a quantitative result. Some analytes, however,
require a digital present/not present signal indicative of a
threshold concentration. `Analog` and/or `digital` formats may be
utilized separately or in combination. Other statistical methods
can be utilized with PMAMS. For instance it is possible to create
concentration gradients of PMAMS on a surface (Chaudhury et al.,
1992, Science 256:1539-1541). This technique is used to determine
concentrations through statistical analysis of binding over the
concentration gradient. Multiple linear arrays of PMAMS with
concentration gradients may be produced with a multiplicity of
different specific binding reagents. The concentration gradients
may consist of discrete binding domains presenting different
concentrations of the binding reagents.
[0217] The presence of control assay systems on the binding surface
of the cassette is also important to assure the uniformity of each
analysis to control for signal variation (e.g., variations due to
degradations, fluctuations, aging of the cassettes and other
components, thermal shifts, noise in electronic circuitry and noise
in the photodetection device, etc.). For example, multiple
redundant binding domains (containing identical binding reagents or
different binding reagents that are specific for the same analyte)
for the same analyte may be utilized. In another example, analytes
of known concentration are utilized or control domains of a PMAMS
are covalently linked to a known quantity of an ECL label or a
known quantity of ECL label in solution is used.
[0218] The assays conducted according to the invention will rapidly
and efficiently collect large amounts of data that can be stored,
e.g., in the form of a database consisting of a collection of
clinical or research information. The data collected may also be
used for rapid forensic or personal identification. For example,
the use of a plurality of nucleic acid probes when exposed to a
human DNA sample can be used for a signature DNA fingerprint that
can readily be used to identify clinical or research samples.
5.7. Preparation of Electrodes for Multi Arrays
[0219] The electrodes may be broadly from 0.001 to 10 mm in width
or diameter. In a preferred range the electrodes are from 0.01 to 1
mm in dimension (width or diameter or widest dimension depending
upon the geometry of the electrodes).
[0220] Preferably, the electrodes are fabricated from suitable
conductive materials, such as transparent metal films or
semiconductors (e.g., gold or indium-tin oxide, respectively), as
is well known to the art, for example, for the fabrication of
liquid crystal displays and the like. In the assembled form of the
cassette, sufficient space remains between the first and second
supports to contain an analytic sample as, for example, a thin film
or a wetted surface.
[0221] The electrodes may be fabricated from materials that contain
carbon, e.g. particulate carbon, carbon black, carbon felts, glassy
carbon, carbon fibers, carbon fibrils and/or aggregates of the
above.
[0222] One or more individual fibrils and/or one or more aggregates
of fibrils may be processed to form a larger aggregate (U.S. Pat.
No. 5,124,075). In one embodiment, this larger aggregate is a mat
or mesh. Hereinafter, the term "fibril mat" will be used to
describe a mat or mesh of fibrils which the fibrils may be
entangled interwoven. Fibril mats can have a surface area between
50 and 400 M.sup.2/gram.
[0223] By way of example, a fibril mat may be used as a working
electrode, a counter electrode or a reference electrode in
analytical and/or preparative electrochemistry. In one example, the
fibril mat is used as an electrode for electrochemiluminescence
(ECL).
[0224] The binding domains of the PMAMS may be supported by an
electrode, e.g. a fibril mat or an electrode formed from carbon
black. The PMAMS of the invention has a plurality of discrete
binding domains, of which two or more may be identical to each
other or may differ. The fibril mat supports one or more binding
domains.
[0225] One or more microfluidic guides may be used to prepare a
plurality of binding domains on a fibril mat. Different or
identical binding reagents may be present in a plurality of
microfluidic guides and/or multiple distinct binding agents may be
present in a microfluidic guide.
[0226] In FIGS. 22A and 22B a plurality of microfluidic guides
2201, preferably in an array, are used to deliver, preferably
concurrently, onto regions of the fibril mat 2200, drops containing
the desired binding reagents, to form discrete binding domains
2202. The binding reagents form a bond with moieties present on the
fibril mat. The binding reagents may adsorb non-specifically to the
mat or dry on the surface.
[0227] The desired binding reagents are delivered to the fibril mat
while suction filtration is applied to the mat. In this instance,
the suction filtration draws none, some or all of the binding
reagents into or through the mat, and in doing so, reduces the
amount of lateral spreading of the binding reagents on the surface
of the mat during the patterning process.
[0228] Fibril mats are prepared by compressing suspensions of
carbon fibrils onto a substrate through which the liquid of the
suspension may pass (e.g., a filter). Examples of filters that may
be used to form fibril mats include filter paper, filters formed
from polymeric (e.g., nylon) membranes, metal micromeshes, ceramic
filters, glass filters, elastomeric filters, fiberglass filters
and/or a combination of two or more of such filter materials. One
of skill in the art of filtration would recognize that these
materials are merely examples of the many possible materials
suitable for filtration of suspensions of solids.
[0229] FIG. 23A and 23B illustrates an embodiment, in which fibril
mats may be fabricated by suction filtration. A dispersion and/or
suspension of carbon fibrils 2301 is filtered using a filter 2300
equipped optionally with a filter membrane 2303 and/or a filter
support 2302. The suspension is filtered using suction applied by a
vacuum source 2305 to the filter by, for example, a filter flask
2306. A fibril mat 2304 collects on either or both the filter
membrane 2303 and/or the filter support 2302. The fibril mat 2304,
with or without the filter membrane 2303 may be removed from the
filter.
[0230] In another embodiment, suspensions of fibrils are forced
through a filter by use of pressure. In one example, pressure is
exerted on a confined suspension of fibrils by compressing a
confined layer of air and/or liquid above the suspension with a
piston. In a specific example, the suspension of fibrils is
confined in a syringe, the piston is a syringe plunger, and the
filter is a disposable syringe filter (many such filters are well
known to one of skill in the art).
[0231] Suspensions of fibrils are forced through a filter by
capillary action or filtered by wicking of the suspension into or
through a filter.
[0232] In another embodiment, individual fibrils or aggregates of
fibrils are crosslinked covalently into mats. Fibrils derivatized
with photosensitive moieties that polymerize when exposed to light
are irradiated with light.
[0233] In another embodiment, individual fibrils or aggregate of
fibrils are sprayed onto a substrate. It is possible to use
electrospray.
[0234] The filter may be used to trap the fibrils in its pores and
so form a mat in which the filter acts as a support. In FIG. 24, a
fibril mat 2400 may be prepared by passing a slurry of fibrils
2401, delivered by a source 2402, between two large rollers 2403.
In this process, which may be analogous to processes found in the
fabrication of paper or polymer sheets, the rollers force the
liquid from the suspension and a large, continuous mat of fibrils
is produced from which smaller mats may be cut.
[0235] Fibril mats may be freestanding (e.g., unsupported) or
supported.
[0236] The rate of filtration can be varied to achieve desired
properties in the mat. For example, properties that may be varied
include uniformity or non-uniformity of structure, the extent of
entanglement of the fibrils or aggregates of fibrils, the
thickness, the porosity of the mat, and/or combinations
thereof.
[0237] Suspensions of carbon fibrils are confined and the liquid in
which the fibrils are suspended is removed. In one example, the
liquid in which the fibrils are suspended is allowed to evaporate.
In another example, the liquid is removed by heating. In yet
another example, the suspension is subjected to centrifugation, and
the resulting liquid (e.g., the supernatant) is removed. In another
example, the liquid is removed by evacuation.
[0238] The suspension may be placed on one or more of the filters
described supra, and the suspension dried by evaporation. The
suspension may be dried by heating or baking in an oven or the
liquid may be removed by freezing and extracting the liquid. In yet
another example, the liquid is removed by evacuation with a pump.
Many other methods which are well known to one skilled in the art
are available for removing liquids from a suspension.
[0239] Suspensions of fibrils suitable for forming fibril mats by
filtration may be formed by dispersing one or more carbon fibrils
in an appropriate liquid, quasi-solid or gel. Examples of
appropriate liquids include but are not limited to water, ethanol,
methanol, hexane, methylene chloride, buffered solutions,
surfactants, organic solvents, solutions of containing biological
media (e.g., as proteins, antibodies or fragments thereof, cells,
subcellular particles, viruses, nucleic acids, antigens,
lipoproteins, liposaccharides, lipids, glycoproteins,
carbohydrates, peptides, hormones or pharmacological agents,
solutions of small molecules, polymer precursors, solutions of
acids or bases, oils and/or combinations thereof).
[0240] A suspension of fibrils may be prepared by dispersing carbon
fibrils in an aqueous solution by means of sonication. In another
embodiment, surfactant and or detergent may be added.
[0241] The fibril mat may have broadly a thickness between 0.01
.mu.m and 10,000 .mu.m.
[0242] In preferred embodiments, the fibril mat has a thickness
between 1 .mu.m and 100 .mu.m. In particularly preferred
embodiments, fibril mats range from 10 mm to 200 mm in width or
diameter.
[0243] The fibril mat may be washed repeatedly and refiltered to
remove residual materials remaining from the suspension.
[0244] Fibril mats prepared by filtration or evaporation are heated
(e.g., in an oven) to remove residual liquid from the suspension
not removed by filtration.
[0245] Successive filtration steps may be used to form mats of
fibrils composed of one or more distinct layers that are either in
contact with or in close proximity to one or more other layers.
Layers may be distinguished by several properties, including but
not limited to differences in the porosity, the density, the
thickness, the distribution of sizes of individual fibrils and/or
microscopic aggregates of fibrils, the type, number and/or size of
fibril aggregates, the chemical derivatization of the fibrils (vide
infra), and/or the presence of other matter attached to the
fibrils.
[0246] FIG. 25, a multi-layered fibril mat 2500 is prepared by
successive filtration steps. A 0.5 .mu.m to 100 .mu.m thick layer
2501 of plain fibrils forms the first layer; a 0.5 to 10 .mu.m
thick layer of fibrils 2502 that incorporate moieties such as
poly-(ethyleneglycols) that resist adsorption of proteins and other
molecules forms the second layer; a 0.5 to 5 .mu.m thick layer 2503
that incorporates one or more binding domains (vide supra) forms
the third layer. The binding domains contain one or more antibodies
2504, which may bind an analyte 2505. This antibody/analyte complex
may bind a labeled antibody 2506. The label may be an ECL label. In
other embodiments, the label may be one or more of a plurality of
labels described elsewhere in this application. Such a multilayer
mat may be freestanding or supported on one of a plurality of
possible supports described above.
[0247] Multilayer mats may be formed in which there are
combinations of layers, in which some or all of the layers may be
different.
[0248] The filter used to form the fibril mat, the fibrils, and/or
the fibril mat may be coated. In particular embodiments, the
coatings are metallic. These coatings may be patterned such that
certain portions are coated, and other portions are not. In one
example, the coating is applied by electrodeposition. In another
example, the coating is applied by electroless deposition. Other
methods of metal deposition, e.g. thermal or electron bean
depositions or sputtering, can also be used.
[0249] The filter is coated with a metal, and the fibril is
derivatized with a chemical functional group that forms a bond with
said metal. The filter is a metal screen or metal sheet.
[0250] The fibril mat may be flat or deformed, regular or
irregular, round, oval, rectangular, or one of many shapes, rigid
or flexible, transparent, translucent, partially or fully opaque
and may have composite properties or regions of different
individual or composite properties.
[0251] The mat may be a disk or a piece taken from a sheet.
[0252] A plurality of fibril mats may be fabricated, preferably
concurrently, and preferably in an array. In one example, an array
of microfluidic guides forms a plurality of fibril mats on a
support as described above. In another example, an array of
filters, or a patterned filter (e.g., with regions of different
porosity) is used to prepare an array of fibril mats.
[0253] A mask with an array of holes (e.g., a screen) is used to
cover certain portions of a filter or support, and a plurality of
discrete fibril mats are made concurrently by either filtration
and/or evaporation.
[0254] Fibril mats may have a density from 0.1 to 3.0
grams/cm.sup.2. The mat may have variable density. For example,
mechanical force or pressure may be applied to the mat at different
times to increase or decrease the density.
[0255] Fibril mats may have pores. These pores may extend partially
and/or fully through the mat or may be part of a network or pores.
These pores may have dimensions ranging broadly from 50 .ANG. to
1000 .mu.m. In a preferred embodiment, the fibril mat has pores
with dimensions ranging from 200 .ANG. to 500 .ANG.. The porosity
of the mat may depend on the density of the mat, among other
factors.
[0256] The porosity of the mat may be constant throughout the mat
or may increase or decrease as a function of the position in the
mat. The fibril mat may have a wide variety of pores of different
size distributed in a disorganized and/or random manner.
[0257] The fibril mat may contain distinct regions of different
porosity. For example, the fibril mat may have one or more layers,
each having a different porosity. The fibril mats may have columns
of different porosity that run through the mat.
[0258] The porosity of the mat may be varied by including different
amounts of aggregates of carbon fibrils, where aggregates have
different size, shape, composition, or combinations. In a
particular example, a mat can be prepared from individual fibrils,
CC fibrils (described supra) and BN fibrils (described supra), or
different combinations. For example, the fibril mat may have some
pores that are large enough to pass objects as large as biological
cells, some pores that can pass biological media as large as
proteins or antibodies, some pores that can pass only small
(<1000 molecular weight) organic molecules, and/or combinations
thereof.
[0259] The porosity of the mat may be such that one or more
molecules, liquids, solids, emulsions, suspensions, gases, gels
and/or dispersions can diffuse into, within and/or through the mat.
The porosity of the fibril mat is such that biological media can
diffuse (actively or passively) or be forced by some means into,
within and/or through the mat. Examples of biological media include
but are not limited to whole blood, fractionated blood, plasma,
serum, urine, solutions of proteins, antibodies or fragments
thereof, cells, subcellular particles, viruses, nucleic acids,
antigens, lipoproteins, liposaccharides, lipids, glycoproteins,
carbohydrates, peptides, hormones or pharmacological agents. The
fibril mat may have one or more layers of different porosity such
that material may pass through one or more layers, but not through
other layers.
[0260] The fibril mat is supported by or on another material. By
way of example, the supporting material may be a metal, plastic,
polymer, elastomer, gel, paper, ceramic, glass, liquid, wax, oil,
paraffin, organic solid, carbon or a mixture of two or more of
each. The material may be solid or liquid. If it is solid, it may
contain one or a plurality of holes or pores. In specific examples,
the support may be a metal mesh, a nylon filter membrane or a
filter paper. The support may be a conductor, a semiconductor
and/or an insulator. The fibril mat may incorporate another
material, for example thin fibers, shards, or balls of metal to
increase the conductivity of the mat. In another example, the
fibril-mat may incorporate other carbon, glass and/or metal fibers
of varying size, shape and density to create a different porosity
than can be achieved with fibrils alone. In another aspect, the mat
may incorporate magnetic beads (for example, DYNAL beads). In the
latter example, the beads may either serve to change a property of
the mat, or may themselves be used as supports to immobilize
binding domains.
[0261] In an embodiment disclosed in U.S. Pat. Nos. 5,304,326 and
5,098,771, fibrils may be dispersed in another material. For
example, fibrils may be dispersed in oils, waxes, paraffin,
plastics (e.g., ABS, polystyrene, polyethylene, acrylonitrile,
etc.), ceramics, teflon, polymers, elastomers, gel, and/or
combinations thereof. Dispersions of fibrils in other materials are
conducting. Dispersions of fibrils in other materials may be
molded, pressed, formed, cast, spun, weaved, and/or thrown so as to
form objects of a desired shape and/or form.
[0262] Other carbon materials (e.g., particulate carbon, carbon
fibers, graphitic carbon, buckminsterfullerenes, fullerenes, or
combinations thereof) may be dispersed in another material. They
can be derivatized with chemical functional groups that can be used
to attach other materials to them. Materials may be attached
covalently to these functional groups, or they may be adsorbed
non-covalently.
[0263] Carbon fibrils may be prepared with chemical functional
groups attached covalently to their surface. As described in
International Publication No. WO 90/14221, these chemical
functional groups include but are not limited to COOH, OH, NH.sub.2
N-hydroxy succinimide (NHS)-esters, poly-(ethylene glycols),
thiols, alkyl ((CH.sub.2).sub.n) groups, and/or combinations
thereof. These and other chemical functional groups can be used to
attach other materials to the surface of fibrils.
[0264] Certain chemical functional groups (e.g., COOH, NH.sub.2,
SH, NHS-esters) may be used to couple other small molecules to the
fibrils. There are a plurality of possible combinations of such
chemical functional groups and small molecules.
[0265] In many embodiments, NHS-ester groups are used to attach
other molecules or materials bearing a nucleophilic chemical
functional group (e.g., an amine). In a preferred embodiment, the
nucleophilic chemical functional group is present on and/or in a
biomolecule, either naturally and/or by chemical derivatization.
Examples of suitable biomolecules include but are not limited to
amino acids, proteins and functional fragments thereof, antibodies,
binding fragments of antibodies, enzymes, nucleic acids, and
combinations thereof. This is one of many such possible techniques
and is generally applicable to the examples given here and many
other analogous materials and/or biomolecules. In a preferred
embodiment, reagents that may be used for ECL may be attached to
the fibril via NHS-ester groups.
[0266] An antibody that can be used in an ECL assay can be attached
to one or more fibrils or a fibril mat by covalent bonds (e.g.,
reaction with an NHS-ester), by reaction with an appropriate linker
(vide supra), by non-specific binding, and/or by a combination
thereof. Nucleic acids and/or cells can be attached to fibrils or
fibril mats by covalent links to NHS-esters attached to the
fibrils.
[0267] It may be desirable to control the extent of non-specific
binding of materials to fibrils and/or fibril mats. Simply by way
of non-limiting examples, it may be desirable to reduce or prevent
the non-specific adsorption of proteins, antibodies, fragments of
antibodies, cells, subcellular particles, viruses, serum and/or one
or more of its components, ECL labels (e.g., Ru.sup.II(bpy).sub.3
and Ru.sup.III(bpy).sub.3 derivatives), oxalates, trialkylamines,
antigens, analytes, and/or combinations thereof. In another
example, it may be desirable to enhance the binding of
biomolecules.
[0268] One or more chemical moieties that reduce or prevent
non-specific binding may be present in, on, or in proximity to a
carbon-containing electrode (e.g. carbon black) or one or more
fibrils, one or more fibril aggregates, a dispersion of fibrils in
another material and/or a fibril mat. Such moieties, e.g., PEG
moieties and/or charged residues (e.g., phosphates, ammonium ions),
may be attached to the electrode.
[0269] Materials used in the support, electrode and/or binding
domain may be treated with surfactants to reduce non-specific
binding. For example, fibrils or fibril mats may be treated with
surfactants and/or detergents that are well known to one of
ordinary skill in the art (for example, the Tween series, Triton,
Span, Brij). The fibrils or fibril mats are washed, soaked,
incubated with, sonicated in, and/or a combination thereof with
solutions of surfactants and/or detergents. Solutions of PEGs
and/or molecules which behave in similar fashion to PEG (e.g.,
oligo- or polysaccharides, other hydrophilic oligomers or polymers)
("Polyethylene glycol chemistry: Biotechnical and biomedical
applications, Harris, J. M. Editor, 1992, Plenum Press) may be used
instead of and/or in conjunction with surfactants and/or
detergents.
[0270] Undesirable non-specific adsorption of certain entities such
as those listed above may be blocked by competitive non-specific
adsorption. This competitive binding species might be bovine serum
albumin (BSA) immunoglobulin G (IgG).
[0271] Non-specific binding of the ECL-TAG may be reduced by
chemical modification of the TAG. For example, the TAG may be
modified so as to increase its hydrophilicity (e.g. by adding
hydrophilic, polar, hydrogen bonding, and/or charged functional
groups to the bipyridyl ligands in Ru(bpy.sub.3)) and thus reduce
non-specific binding of the TAG to other surfaces.
[0272] It may be desirable to immobilize biomolecules or other
media to carbon-containing materials, e.g. carbon black, fibrils, a
fibril mat, and/or carbon dispersed in another material. One may
attach antibodies, fragments of antibodies, proteins, enzymes,
enzyme substrates, inhibitors, cofactors, antigens, haptens,
lipoproteins, liposaccharides, cells, sub-cellular components, cell
receptors, viruses, nucleic acids, antigens, lipids, glycoproteins,
carbohydrates, peptides, amino acids, hormones, protein-binding
ligands, pharmacological agents, and/or combinations thereof. It
may also be desirable to attach non-biological entities such as,
but not limited to polymers, elastomers, gels, coatings, ECL tags,
redox active species (e.g., tripropylamine, oxalates), inorganic
materials, chelating agents, linkers etc.
[0273] One or more or a plurality of species may become bound
non-specifically (e.g., adsorb) to the surface of a material
comprised of carbon.
[0274] Biological molecules or other media can be attached to
fibrils or fibril mats by non-specific adsorption. The extent of
non-specific adsorption for any given fibril, fibril mat and/or
biomolecule will be determined by certain properties of each.
Certain chemical functional groups or biological moieties present
on fibrils may reduce or enhance non-specific binding. The presence
of hydrophobic and/or hydrophilic patches on the surface of a
protein may enhance or reduce non-specific binding of the protein
to fibrils or fibril mats. Hydrophilic and/or hydrophobic patches
are utilized to control non-specific binding in controlled
areas.
[0275] Carbon can be derivatized with alkyl (CH.sub.2) chains
and/or carboxylic acid groups to enhance non-specific binding of
biological molecules or media or other materials.
[0276] FIG. 26 illustrates the above embodiment schematically in
the case of a single fibril. A fibril 2600 is derivatized with
alkyl chains 2601. Biomolecules 2602, 2603, and 2604 bind
non-specifically to the alkyl chains. Polymer/elastomer 2605 is
also bound.
[0277] Underivatized fibrils, fibril aggregates and/or fibril mats
are used for immobilization of biomolecules, biological media, and
other materials by non-specific binding.
[0278] The ECL TAG may contains charged residues that could be used
to selectively attract a TAG-labeled moiety to a support and/or
electrode. For example, a derivatized ECL TAG which has a net
negative charge may have a relatively low affinity for an electrode
at more reducing potentials and then have higher affinity for the
electrode as the electrode potential becomes more oxidizing. The
affinity of the ECL label and/or binding reagents to the electrode
may be made to modulate. This modulation may be used to improve the
kinetics of binding or improve the efficiency of a washing
step.
[0279] In FIG. 28 molecules (both biological and non-biological)
may be attached to fibrils by means of a covalent bond. Fibrils
2800 bearing an NHS-ester chemical functional groups may form
covalent bonds 2801 to biomolecules or biological media 2802,2803.
These biological media may use an amino group to form a covalent
bond by reaction with the NHS-ester group. Polymer 2808 is
immobilized. One of ordinary skill in the art would recognize the
generality of NHS-ester groups as coupling agents for molecules and
would be able to select both the appropriate biomolecules and the
appropriate reaction conditions to achieve immobilization.
[0280] A pair of moieties and/or molecules "M1" and "S1", of which
one or more is attached to a fibril, exhibit a mutual affinity or
binding capacity. M1/S1 may be antibody/antigen, antibody/hapten,
enzyme/substrate, enzyme/cofactor, enzyme/inhibitor,
lectin/carbohydrate, receptor/hormone, receptor/effector, nucleic
acid/nucleic acid, protein/nucleic acid, virus/ligand,
cell/cellular receptor, etc. Many combinations of "binding pairs"
M1/S1 and would be able to select combinations appropriate to
achieve the desired binding. Either or both M1 and S1 may be
attached to one or more fibrils.
[0281] FIGS. 27 and 28 illustrate some of the many possible
configurations that are possible with this embodiment. In FIG. 27,
a fibril 2700 derivatized with alkyl chains 2701 non-specifically
binds a molecule 2702 that has a mutual affinity or binding
capacity for another molecule 2703. Molecule 2703 is also attached
to another molecule 2704. A blocking molecule 2705 may be
non-specifically adsorbed to the fibril. A blocking polymer 2706
and/or a polymer 2707 which has a ligand (2708) that has an
affinity for a molecule 2709 are non-specifically adsorbed.
[0282] In FIG. 28, a fibril 2800 is covalently linked via 2801 to
biomolecules 2802 and 2803, and a linker molecule 2804. The linker
molecule 2804 has a mutual affinity or binding capacity for another
biomolecule 2805. Biomolecule 2803 has a mutual affinity or binding
capacity for another linker molecule 2806, which is covalently
linked to 2807. Polymer 2808 with a ligand 2812 that is specific
for a binding partner 2809 is covalently linked to a fibril.
Blocking molecules (e.g. BSA) 2811 and blocking polymers 2810 are
covalently attached.
[0283] A fibril may be derivatized with biotin and/or a
biotinylated linker and avidin and/or streptavidin may bind to this
linker. Avidin and/or streptavidin may be bound to the fibril, and
a biotinylated antibody and/or protein may bind. Avidin and/or
streptavidin may be immobilized on the fibrils by either
non-specific binding, covalent bond, another or the same coupling
pair, or a combination thereof. The use of (strept)avidin and
biotin as "binding pairs" is a widely applied method of attaching
biomolecules or biological media to other materials and is well
known to those skilled in the art (Spinke et al., 1993, Langmuir
9:1821).
[0284] A binding pair may be a monoclonal antibody and an antigen
that binds to this antibody.
[0285] Multiple binding pairs (e.g., M1/S1/M2) may form. M1 is a
monoclonal antibody, S1 is an antigen to M1, and M2 is an antibody
that binds to S1. This complex may constitute an
antibody/antigen/antibody "sandwich" complex (such antibodies may
or may not be monoclonal). M2 may be an antibody tagged with an
ECL-active tag (vide supra), a fluorescent label, a radioactive
label, an enzymic tag, and/or combinations thereof.
[0286] M1 may be a moiety that can complex with a metal, metal ion,
or organometallic compound (a "chelating agent") and S1 is a metal,
metal ion, or organometallic compound (a "chelates") that forms a
complex with M1, and M2 is a moiety on a biological molecule that
binds to the M1/S1 complex (Gershon and Khilko, 1995, Journal of
Immunological Methods, 7371).
[0287] The fabrication of metallic electrode patterns and
conductive elements to distribute electrical current to such
electrodes on a surface is carried out by methods well known to the
art (see, e.g., Leventis et al., U.S. Pat. No. 5,189,549). The
preparation of metal films on transparent surfaces is used to
produce liquid crystal displays and is readily adapted to the
preparation of electrodes according to the invention. Haneko, 1987,
Liquid Crystal TV Displays, Principles and Applications of Liquid
Crystal Displays, KTK Scientific Publishers, Tokyo, D. Reidel
Publishing. Transparent electrode surfaces may also be prepared,
for example, according to the method of DiMilla et al., 1994, J.
Am. Chem. Soc. 116(5):2225-2226. 0.5 nm of titanium and 5 nm of
gold are deposited on transparent substrates (glass or plastic). A
thin gold layer as prepared by the method of DiMilla, supra may be
used to prepare a transparent electrical structure by the method of
Kumar supra. Modifications of this procedure to increase the
thickness of the conductor layers for improved current carrying
capacity while preferably maintaining transparency are desirable
and readily apparent to the ordinary artisan. Such techniques may
be used to prepare electrode surfaces that are aligned with or in
proximity with discrete binding domains of a PMAMS.
[0288] In addition, the films and/or monolayers may be composed of
moieties which facilitate the transfer of electrical potential from
the electrode surface to the ECL label, rather than using
insulating moieties (e.g., alkyl chains) as taught by Zhang and
Bard. For example, pi orbital overlap in extensively conjugated
systems can be used for electron transfer. Such pi orbital electron
transfer is provided by poly-pyrole or other conjugated rings or
double bonded structures.
[0289] Oligonucleotides may be utilized to modulate electron
transfer. For example, overlapping pi bonds in double stranded DNA
may be utilized to increase electron transfer rates.
Oligonucleotides bound to an electrode surface can be utilized as a
binding agent in a binding domain. Upon binding a complementary
oligonucleotide sequence a double strand with organized overlapping
pi bonds is formed. In a particular embodiment, a first or primary
immobilized (e.g., covalently linked to a support) oligonucleotide
is ECL labeled. In another embodiment a secondary complementary
oligonucleotide or oligonucleotide of partially complementary
sequence to the primary oligonucleotide is ECL labeled. A tertiary
oligonucleotide complementary to or partially complementary to the
secondary oligonucleotide is labeled (e.g., a sandwich assay).
Branched oligonucleotide chains may also be utilized. A variety of
oligonucleotides and/or oligonucleotide mimics can be utilized
(e.g., oligonucleotides with modified bases and/or modified
backbones containing for example nitrogen and/or sulfur).
Differential studies may be performed. Variable stability of pi
overlap in oligonucleotides and/or oligonucleotide complexes may be
monitored through modulation of electron transfer. The signal
(e.g., ECL light generated and/or impedance measurements) generated
from a pi bond stabilized ECL labeled double helical
oligonucleotide pair may be correlated against the signal and/or
expected signal from a more disordered single stranded
oligonucleotide. The variation in ECL signal between a fully
complementary ECL labeled double stranded oligonucleotide and a
partially complementary ECL labeled double stranded oligonucleotide
may be correlated. Additionally, oligonucleotide complexes of
multiple oligonucleotides may be utilized. For example, triple
helices may be employed.
[0290] Modulation of electron transfer rates may be measured using
ECL detection as well as electronic means. ECL labels may be
covalently linked to oligonucleotide strands and/or non-covalently
associated (e.g., intercalated). DNA may be coupled to the
electrode without the use of a linker (e.g., adsorption of 5'
thiolated DNA on gold) or with a short (<10 atom) linker to
ensure low resistance to electron transfer from the DNA to the
electrode. A linking chain may be used that can efficiently
transport electrons from the electrode to the DNA strand (e.g., a
polyacetylene chain).
[0291] A mixed monolayer and/or film may be used in which at least
one constituent of the monolayer or film, as the case may be,
facilitates the transfer of electrical potential. Alternatively, a
molecule or particle that facilitates the transfer of electrical
potential is adsorbed to the monolayer or film. As examples of the
foregoing, the pi conjugated monolayers and/or conducting
micro-particles which adsorb to and/or are approximate to the
electrode surface, may be used. Patterned regular gaps are created
in the monolayer and or film. By utilizing controlled patterns of
gaps in an ordered substantially perpendicular SAM composed of long
chain alkane thiols (i.e., insulating) to which ECL labels have
subsequently been attached, the effective potential imposed at the
ECL labels can be controlled. For example, FIG. 11 shows a cassette
1200 formed of a single support 1202 with a metallic layer 1204, a
SAM pattern 1206 and gaps 1208 between the SAM patterns.
[0292] ECL labeled proteins may be non-covalently linked to a
monolayer surface. An ECL labeled protein may adsorb to the surface
of a methyl terminated alkane thiol derivatized gold surface. The
gold surface may act as the working electrode or the counter
electrode. A plurality of binding domains may be incorporated on a
single support as is illustrated in FIGS. 11-13. In preferred
embodiments the binding domains contain labelled and/or unlabelled
proteins and/or nucleic acids and/or cells and/or chemical
species.
[0293] Alternatively, the length of the components of the monolayer
(e.g., the length of the alkane chain in alkane thiol monolayers)
may be varied to control the effective potential at the exposed
surface of the monolayer.
[0294] Broadly, alkane thiols may have carbon chains of length
between 1 carbon and 100 carbons. In a preferred embodiment the
carbon length of the alkane thiol contains between 2 and 24
carbons. The carbon chain length of the alkane thiol is between 2
and 18 carbons. The carbon chain length is between 7 and 11
carbons. Such alkane thiols may have a variety of head groups
exposed to the assay media including methyl groups, hydroxy groups,
amines, carboxylic acids, oligo (ethylene glycols), phosphate
groups, phosphoryl groups, biotin, nitrilotriacetic acid,
glutathione, epoxides, dinitrophenyl, and/or NHS esters. Other head
groups include ligands commonly used for the purification and
immobilization of recombinant fusion proteins (e.g., Sassenfeld,
1990, TIBTECH 8:88-93). The binding domains may be derivatized to
varying degrees to achieve varying densities of binding reagents.
For example, different densities of activatable chemistries may be
used and/or derivatization may be carried out to varying extents.
Mixed chemistries may be utilized to create desired binding
densities. Mixed monolayers may be utilized to control the density
of activatable groups and/or binding reagents. The density of
binding groups is controlled to optimize the ECL signal to noise
ratio. The total number of binding sites within a binding domain(s)
is controlled to optimize the intensity of the ECL light signal
with respect to other ECL light signals from other binding
domain(s) whether such ECL light signals are detected sequentially
or simultaneously and/or with respect to the light detection
means.
[0295] The voltage waveform may be applied so as to activate ECL
labels associated with a binding domain(s) within a PMAMS one or
more times. An electronic potential sufficient to activate ECL
light generation may be applied multiple times to the same alkane
thiol derivatized surface with bound ECL label to generate multiple
ECL light signals. Electronic potential is applied sufficiently to
generate ECL reversibly. Potential is applied so as to generate ECL
quasi-reversibly. In a quasi-reversible series of voltage waveforms
the binding domain within which ECL label associates (e.g., binds),
may be chemically and/or physically altered. The voltage waveform
series applied may yield irreversible ECL light generation.
[0296] Further, an electric potential sufficient to release the
components of the monolayer may be applied. It is desirable to
release such monolayer components where the volume above the
electrode surface is small (e.g., another support or plate resting
on the electrode surface). In this way as the monolayer is
disrupted, even some ECL labels that are not efficiently excited
may be excited by the electrode surface to generate the
electrochemiluminescent signal and the ECL labels are restricted to
a small volume restricting diffusion from the electrode. Various
monolayer compositions may be utilized to control the degree of
monolayer disruption for a given potential. Monolayers with
components with strong inter-component affinity will be more
resistive to monolayer disruption. Longer alkane chain thiols
resist disruption more effectively than short alkane chain thiols.
By varying the chain length the desired stability may be
achieved.
[0297] Modification of the binding domains within a PMAMS may be
used to modulate the ECL signal. A series of voltage waveforms is
applied so as to generate a multiplicity of ECL signals. Said
multiplicity of ECL signals may be utilized to gain extra and/or
better results. Statistical analysis of the rate of modulation of
the ECL signal may be correlated to the overall quality of one or
more binding domains. Additionally, said multiplicity of ECL
signals may be utilized to increase signal to noise by, for
example, filtering certain ECL signals of a series. Further,
multiple electronic potential waveform pulses may be utilized to
reduce undesirable modulation of signal due to non-specific
binding. Electronic potential may be applied to prevent
non-specific binding of certain charged species. Additionally,
electronic potential may be applied so as to promote the
localization near a binding domain(s) of certain analytes or
chemical species of interest. The voltage waveform applied supplies
large over-potential (e.g., higher potential than is required to
generate ECL). Over-potentials may be utilized to modulate ECL
signals in a voltage wave series or in a single voltage wave pulse.
Additionally, over-potentials may be utilized to modulate the ECL
reaction kinetics and/or modulate the binding potential chemically
and/or physically. Further, one or more voltage waveforms and/or
other electronic probes known to those skilled in the art may be
utilized to assess and/or correlate and/or extrapolate information
on the quality and/or electronic properties of an electrode(s).
[0298] Preferably, the efficiency of the ECL reaction may be
enhanced by extending the working electrode surface area by
providing additional conducting means in contact with the
electrodes. Projections or extensions from the electrode (e.g.,
wires or whiskers) of conducting materials or conducting particles
may be used to increase the electrode surface area, such that the
electrical field and more closely approaches the ECL label.
Alternatively, indentations or wells in the electrode structures
may serve the same purpose.
[0299] In particular, conductive particles may fill the gaps on the
electrode surface and/or cover the support or monolayer so that the
electrical field around the ECL label is increased in absolute
magnitude, as shown by FIG. 12. These conductive particles extend
the electrode surface area and thereby increase the efficiency of
the ECL reaction. FIG. 12 shows a cassette 1300 having a support
1302 bearing a patterned SAM 1306 on a metallic layer 1304 and
indicates conducting micro-particles filling in the gaps (e.g.,
1208 in FIG. 11) and extending above the metallic surface between
the SAM patterns. For magnetic conducting particles, a magnet or
magnetic field may be used to draw the particles to the surface.
The conductive particles may also be used as described to extend
the electrical potential between the electrode surfaces and the
binding domain of a PMAMS with two approximated supports. In FIG.
8, the cassette 900 consists of a first support 902 that has a
multi array of electrodes, and a second support 904 that has a
PMAMS. Conducting micro-particles 906 are positioned between the
opposing surfaces in order to extend the electrical potential
toward the ECL label on the binding domains (not shown).
[0300] Alternatively, conductive polymers are grown from the
exposed gaps on the electrode surface to facilitate extending the
electrical potential around the ECL label of the sample as shown by
FIG. 13. FIG. 13 shows a cassette 1400 having a support 1402
bearing a metallic layer 1404 on a patterned SAM surface 1406.
Conductive polymers 1408 are grown over the SAM surface to extend
the electrical field provided by a multi array of electrodes (not
shown) to binding domains (not shown) on the SAM surface. The
conductive polymers may also be used as described to extend the
electrical potential between the electrode surfaces and the binding
domains of a PMAMS of two approximated supports as illustrated by
FIG. 7. In FIG. 7, the cassette 800 consists of approximated
supports 802 and 804. Conductive polymers 806 are grown between the
opposed surfaces so as to extend the electrical potential toward
the ECL label on the binding domain (not shown).
[0301] FIG. 9 illustrates a cassette 1000 formed with a first
support 1002 having a multielectrode array, a second support 1004
having a PMAMS binding surface, wherein conductive projections
(1006) (e.g., fine wire or other protrusions) of the working
electrode extend the electrical field around the ECL label in the
PMAMS binding domains.
[0302] The electrode pairs may be created in a variety of
configurations. The simplest configurations, depicted in the
figures accompanying this disclosure, are made of metal and/or
metal oxide films and/or semiconductor films applied on a
non-conducting planar surface. The electrodes of these electrode
pairs preferably define between them a region of relatively
constant width thereby providing a relatively constant electrical
field.
[0303] Other configurations of the electrodes are provided. Several
of these configurations are shown in plane views in FIGS.
19(a)-(e). FIG. 19(a) shows an inter-digitated comb-like electrode
pair. In this structure, each electrode has a plurality of digits
extending from the conductor making a comb-like shape. The
electrode and counterelectrode pair may be positioned adjacent to a
binding domain, or a binding domain may be positioned between an
electrode and counterelectrode. FIG. 19(b) shows a pair of
concentric electrodes, one circular and one semicircular. FIG.
19(c) shows two semicircular electrodes with their straight edges
facing each other. FIG. 19(d) shows a pair of rectangular
electrodes. FIG. 19(e) shows a pair of interdigitated electrodes
having complementary opposing curved surfaces to form a sinuous gap
therebetween.
[0304] The electrode/counterelectrode pairs may also be formed into
specific shapes complementary to shapes on the PMAMS binding
surface for alignment purposes. Exemplary shapes are shown in FIG.
6B. A support 712 bearing electrode pairs 714-720 is shown. The
electrode pairs may be, e.g., circular 714, interdigitated 716
triangular interdigitating 718 or multi electrode interdigitating
720.
[0305] In the embodiments shown in FIGS. 14-19 discussed supra, the
electrode pairs are located on a single support. Alternatively, the
electrode pairs are located on first and second opposing supports
as shown by FIG. 2.
5.8. Cassettes
[0306] Cassettes contain one or more supports of the invention.
Cassettes may include a plurality of binding domains and one or
more working electrodes.
[0307] FIG. 2 depicts a cassette where each of plural binding
domains 30 on support 26 are adjacent to a different one of plural
electrodes 32. Counterelectrodes 38 are formed on a second support
28. An ECL assay is conducted as previously described by placing a
sample on binding domains 30 and then moving together supports 26
and 28 so that counterelectrodes 38 are each adjacent to each of
binding domains 30 and an ECL reaction may be triggered as
described above by waveform generator means 39, via a lead 34, and
an ECL signal detected and recorded by light detector means 40,
wire 41, and digital computer means 42.
[0308] FIG. 3 illustrates a cassette where each of plural binding
domains 48 has a different one of plural electrode/counterelectrode
pairs 50 adjacent thereto on support 44. Support 46 may optionally
be placed adjacent to support 44 so that support 46 forms a sample
containing means adjacent to plural binding domains 48 and plural
electrodes 50. Thus, an ECL reaction may be triggered via
electrical connection 52 by waveform generator means 54, and an ECL
signal detected by light detector means 56 and recorded and
analyzed by digital computer means 58.
[0309] A cassette is provided that contains one or more pairs of
supports as shown in FIG. 21, each pair of supports being situated
so that the surface of a first support 1501 that contains binding
domains faces the surface containing binding domains on the second
support 1502, in which each surface contains electrodes 1504 and
binding domains 1506; such that each binding domain on the first
support faces and is aligned with an electrode on the second
support, and each binding domain on the second support faces and is
aligned with an electrode on the first support.
[0310] FIG. 4 illustrates a cassette wherein ECL electrodes are
optional. Binding domains 64 on support 60 are contacted with a
sample suspected of containing an analyte. Regions 66 on support 62
contain reaction medium for detecting or measuring an analyte of
interest or for carrying out a desired reaction. Support 60 and
Support 62 are brought together so that binding domains 64 and
regions 66 are contacted and the presence of an analyte or reaction
product is determined by a reporter system, e.g. a colorimetric
chemiluminescent or fluorescent signal that may be detected by
photodetector means 68 and recorded and analyzed by digital
computer means 70.
[0311] In a preferred embodiment, a cassette or apparatus of the
invention comprises a means for sample delivery onto the plurality
of discrete binding domains (see, e.g., element 1 on FIG. 1 of U.S.
Pat. No. 5,147,806; element 1 on FIG. 1 of U.S. Pat. No. 5,068,088;
each of which is incorporated by reference in its entirety). The
means for sample delivery can be stationary or movable and can be
any known in the art, including but not limited to one or more
inlets, holes, pores, channels, pipes, microfluidic guides (e.g.,
capillaries), tubes, spigots, etc. Fluids can be moved through the
system by a variety of well known methods, for example: pumps,
pipettes, syringes, gravity flow, capillary action, wicking,
electrophoresis, pressure, vacuum, etc. The means for fluid
movement may be located on the cassette or on a separate unit. The
sample can be placed on all of the binding domains together.
Alternatively, a sample may be placed on particular binding domains
by a capillary fluid transport means. Alternatively, samples may be
placed on the support by an automatic pipetter for delivery of
fluid samples directly to the PMAMS on a support, or into a
reservoir in a cassette or cassette holder for later delivery
directly to the binding surface.
[0312] Supports may be prepared from materials including but not
limited to, glass, plastic, ceramic, polymeric materials,
elastomeric materials, metals, carbon or carbon containing
materials, alloys, composite foils, silicon and/or layered
materials. Supports may have a wide variety of structural, chemical
and/or optical properties. They may be rigid or flexible, flat or
deformed, transparent, translucent, partially or fully reflective
or opaque and may have composite properties, regions with different
properties, and may be a composite of more than one material.
[0313] Reagents for conducting assays may be stored on the cassette
and/or in a separate container. Reagents may stored in a dry and/or
wet state. In one embodiment, dry reagents in the cassette are
rehydrated by the addition of a test sample. Reagents for
conducting ECL assays include ECL coreactants (e.g. TPA), buffers,
preservatives, additives, excipients, carbohydrates, proteins,
detergents, polymers, salts, biomolecules, inorganic compounds,
lipids, and the like. In a different embodiment, the reagents are
stored in solution in "blister packs" which are burst open due to
pressure from a movable roller or piston. The cassettes may contain
a waste compartment or sponge for the storage of liquid waste after
completion of the assay. In one embodiment, the cassette includes a
device for preparation of the biological sample to be tested. A
filter may be included for removing cells from blood. In another
example, the cassette may include a device such as a precision
capillary for the metering of sample.
[0314] The plurality of binding domains and the plurality of
electrodes/counterelectrodes on the supports are typically placed
in registered proximity to one another by mechanical means, e.g.,
by using guide posts, alignment pins, hinges (between each support)
or guide edges. Optical guide means may be used to position both
supports and electronic means utilizing optical guide marks defined
on the supports. Other systems using electrical or magnetic
registration means are also available.
[0315] The supports of the cassette may be configured so as to
protect the electrode pairs from contact with the sample until
required to trigger an ECL reaction. For example, the electrodes
may be kept separate from a binding domain surface until electrode
contact with the sample is required by using various mechanical
means such as a removable electrode protective means.
[0316] A cassette or apparatus of the invention comprises reference
electrodes, e.g., Ag/AgCl or a saturated calomel electrode
(SCE).
[0317] The supports may be held together by clips, adhesive,
rivets, pins or any other suitable mechanical attachment. They may
also be held together by the surface tension of a liquid sample or
by a compression means removably placed on opposite sides of the
two supports.
[0318] The cassette may also comprise more than two supports, with,
for example, alternating layers of binding domains and electrodes
or multiple supports comprising both a binding surface and an
electrode surface on a single support. This will form a three
dimensional array of ECL analysis cells. All of the foregoing
components of the cassette are transparent, except, optionally,
some areas between the binding domains. For example, multiple
transparent binding surfaces, electrode surfaces, and supports may
be stacked.
[0319] The first and second supports may be flat and opposed to
define a sample-holding volume therebetween. Alternatively, the
first and second support layers may be configured in other suitable
shapes including spheroidal, cuboidal, cylindrical, provided that
the two supports, and any other components thereof, conform in
shape. For example, FIG. 10 shows a cassette 1100 formed from two
adjacent non-planar supports 1102 and 1104. Each support has a
surface complementary to the other in conformation. Either support
may have a PMAMS surface or a multi electrode array or both. One or
both of the supports may be elastomeric so as to conform to the
shape of the other support. The supports or the cassettes may also
be prepared in a precut format, or dispensed in a suitable length
from a roll dispenser. The cassette may further include sample
receiving means such as a sample-holding volume and sample
distribution grooves, channels, indentations and the like.
[0320] FIG. 37 shows a cassette where binding domains (3702) in
and/or on a matrix (3703) are presented on a surface (3701). A
second surface (3700) supporting a working electrode (3704) and a
counter electrode (3705) is placed so that the binding domains are
in close proximity to the working electrode. Under conditions which
lead to light generation from ECL label bound to the binding
domains, light may be detected through either or both surfaces. An
array of light detectors (3706, e.g., a CCD array, an intensified
CCD array, or an avalanche photodiode array) is used to
simultaneously measure the plurality of light signals from each of
the binding domains. The light detector array images the light
generated from binding domains. Lenses, reflectors and/or optical
guides may be utilized to enhance imaging. In other examples, light
detected from zones or regions of light detectors (e.g., a light
detecting pixel(s)) is correlated to a binding domain(s). Image
analysis may be used to aid in the correlation of detected light
with binding domains. In one favored embodiment, the surface is
elastomeric or compliant and therefore capable of making intimate
contact with the electrode surfaces. The binding domains are linked
to polymers capable of carrying ionic currents from the counter
electrode to the working electrode. In a more favored embodiment,
the objects are water-swollen polymers capable of carrying an ionic
current from the counter electrode to the working electrode.
[0321] FIG. 38 shows a cassette where binding domains (3805, 3806,
3807) are presented on the surfaces of distinct objects (3808,
3809, 3810) supported on the counter electrode (3800). A working
electrode (3801) is placed in proximity to the surface of the
objects. Under conditions which lead to ECL from TAGged groups
bound to the binding domains, light may be detected through either
or both of the electrodes (if one or both of the electrodes is
transparent or semi-transparent) and/or from the side. An array of
light detectors (3802) is used to simultaneously measure the
plurality of light signals from each of the binding domains. The
objects may be elastomeric and/or compliant and are therefore
capable of forming intimate contact with the working electrode. The
objects may be polymers capable of carrying ionic currents from the
counter electrode to the working electrode. The objects may be
water-swollen polymers capable of carrying an ionic current from
the counter electrode to the working electrode.
[0322] A transparent support containing one or more binding domains
is brought into contact with a carbon electrode, e.g. a fibril mat
electrode or an electrode comprised of carbon black or carbon felt.
Reagents may be flowed either between the support/binding domains
and the fibril mat, or through the mat to the binding domains.
Light may pass from the binding domains, through the transparent
support to a detector.
[0323] In another preferred embodiment, an electrode is coated with
an optically translucent or transparent layer of carbon (e.g.
fibrils) so as to increase the effective surface area of the
electrode.
[0324] Advantageously, the PMAMS supports and/or cassettes of the
invention may be packaged as kits. The kit comprises one or more
PMAMS supports prepared according to the invention for conducting
ECL reactions including assays, controls and the like. Reagents may
be optionally included in the kit, including control reagents, ECL
assay and calibration reagents and the like. A reagent mixture may
be included which contains a plurality of binding reagents specific
for a plurality of different analytes.
5.9. Apparatus for Conducting ECL Reactions
[0325] In one embodiment, the PMAMS on supports, and cassettes
containing the same, are designed to be inserted into an apparatus,
that contains means for applying one or more test samples onto the
PMAMS binding domains and initiating a plurality of ECL reactions.
Such apparatus may be derived from conventional apparatus suitably
modified according to the invention to conduct a plurality of ECL
assays based on a support or cassette. The invention provides
various apparatus adapted to carry out ECL assays using each of the
specific embodiments of PMAMS described in the Sections
hereinabove. An apparatus for conducting ECL reactions is disclosed
by Zoski et al. (U.S. Pat. No. 5,061,445). Modifications required
include the provision for support and/or cassette handling,
multiple sample delivery, multiple electrode addressing by a source
for a voltage waveform and multiple ECL signal acquisition and
processing.
[0326] Elements of illustrative apparatus in accordance with the
invention are shown in FIG. 6A. Such apparatus 700 comprises upper
and lower supports 702, 704 and an electrode guard 710. The upper
support bears a plurality of electrode/counterelectrode pairs (not
illustrated). The lower support bears the binding domains 706. The
apparatus is capable of removing the electrode guard from the
cassette and positioning the electrode/counterelectrodes to contact
the analyte bound to the binding domains. A reagent or fluid flow
space 708 is adjacent to the support bearing the binding domains.
The apparatus is also capable of simultaneously or sequentially
sending an identical or individually determined voltage wave to
each of the plurality of electrode/counterelectrode pairs to
trigger ECL reactions in the cassette and then measuring the
emitted ECL radiation, by a photon detector, e.g., light detector
means. The apparatus can further comprise temperature control means
for maintaining the temperature of the support and/or cassette, or
the environment thereon and adjusting the temperature as needed to
optimize ECL reaction conditions. Temperature control means are
preferably heating and cooling means, e.g., electrical resistive
heating elements, cooling fans, refrigeration means, and any other
suitable source of heating or cooling. Temperature control means
also includes temperature sensors, e.g., a thermostat or
thermocouple device, and means to turn the heating or cooling means
on or off in response to detected temperature changes.
[0327] The apparatus also provides means to hold, move and
manipulate one or more supports or cassettes to conduct ECL
reactions. The apparatus may further comprise a stationary or
moveable sample delivery means for placing a sample onto the PMAMS
binding domains, as described for cassettes hereinabove.
[0328] The apparatus also comprises an electrode contact means able
to electrically connect the array of separately addressable
electrode connections of the cassette to an electronic voltage
waveform generator means, e.g., potentiostat (see e.g., FIG. 5 of
U.S. Pat. No. 5,068,088). The waveform generator means delivers
signals sequentially or simultaneously to independently trigger a
plurality of ECL reactions in the cassette.
[0329] During an ECL assay, ionic current between working and
counter electrodes may flow through ionically conducted liquid (for
example water containing ionic salts), through a thin film of such
liquid, and/or through an ionically conducting solid matrix.
[0330] Thus, an apparatus for measuring electrochemiluminescence in
a sample can comprise a plurality of cells for holding at least one
sample, wherein a cell may be formed from one or more electrodes
and one or more counterelectrodes and a first support that
comprises a plurality of discrete binding domains. The electrodes
and counterelectrodes can be provided on the surface of the first
support or on the surface of a second support wherein the second
support is in close proximity to the binding domains on the first
support. The electrodes and counterelectrodes may occur in pairs.
The cell may further comprise a plurality of sensing electrodes to
sense the voltage adjacent to the working electrode. The cassette
may further comprise a cell containing a reference electrode.
[0331] The apparatus further comprises light detection means able
to detect ECL reactions conducted in the cassette, e.g., by one or
multiple detector means. Such detector means include, simply by way
of example, an array of fiberoptic channels in register with the
electrode array and positioned adjacent thereto, connected to an
array of photodetector means, or to a single light detector means
able to scan the array of ECL signals as emitted.
[0332] The apparatus optionally comprises a digital computer or
microprocessor to control the functions of the various components
of the apparatus.
[0333] The apparatus also comprises signal processing means. In one
embodiment, and simply by way of example, the signal processing
means comprises a digital computer for transferring, recording,
analyzing and/or displaying the results of each ECL assay.
[0334] Alternatively, the apparatus comprises electrode translation
means, for example, to scan one or more electrode/counterelectrode
pairs across the binding surface to sequentially trigger ECL.
[0335] Size exclusion filters may be used in a parallel array of
PMAMS.
5.10. ECL Assays that May be Conducted
[0336] ECL labels for use according to the present invention can be
selected from among ECL labels known in the art (see Section 2.2,
above, and U.S. Pat. No. 5,310,687). The ECL label may comprise,
for example, a metal-containing organic compound wherein the metal
is selected from the group consisting of ruthenium, osmium,
rhenium, iridium, rhodium, platinum, palladium, molybdenum,
technetium and tungsten. Suitable linking chemistry for preparing
ECL TAG reagents is well known and disclosed, for example, by Bard
et al. (U.S. Pat. Nos. 5,310,687 and 5,221,605). The means of
attachment of the ECL label to a binding reagent may be covalent
and/or noncovalent. An ECL label may bind non-covalently to a
binding reagent (e.g., through hydrophobic effects or ionic
interactions). In other examples of non covalent attachment, ECL
label(s) are bound (covalently or non-covalently) to a complex
which in turn is non-covalently linked to a binding reagent. A more
specific example would be covalent attachment of Ru(bpy)3 through a
linker to a Ni(II)-trinitrilotriacetic acid complex. This molecule
will attach to binding reagents which include a peptide sequence
containing a plurality of histidines. Other receptor ligand pairs
are known in the art which can be used in a similar fashion
(Sassenfeld, 1990, TIBTECH 8:88-93). Furthermore, an ECL label can
be used that contains a multiplicity of organometallic compounds
(e.g., Ru-containing) configured as a branched network (e.g.,
through a network of hydrocarbon linkers). Such branched networks
containing a multiplicity of organometallic moieties capable of ECL
may be attached once or attached at a plurality of positions on a
molecule to be ECL labeled. In another embodiment, the ECL label
containing a multiplicity of organometallic compounds is a linear
polymer with the organometallic groups attached at a plurality of
positions along the length of the polymer chain (e.g., linear,
branched or cyclic polymers).
[0337] A plurality of binding domains may be used in a variety of
additional ECL assay formats well known to the art. In quantitative
assays, a known amount of ECL labeled reagent is used and the
amount of ECL measured is correlated to known standards to
calculate the amount of analyte present. Forward, reverse,
competitive and sandwich assays can be performed by methods well
known to the skilled worker. In competitive assays, for example, a
method for quantitatively determining the amount of an analyte of
interest in a volume of multicomponent, liquid sample is performed
as follows. The binding surface is contacted concurrently with (a)
a known amount of an ECL labeled ligand that is capable of
competing with the analyte of interest in binding to a binding
reagent present on the binding domains, and (b) sample suspected of
containing the analyte of interest; the contacting being effected
under appropriate conditions such that the analyte of interest and
the ligand competitively bind to the binding reagent. The presence
of the analyte in the sample will reduce the amount of competing
ECL-labeled ligand that binds to the binding domain, thus reducing
(relative to when no analyte is present in the sample) the
resulting amount of ECL. ECL in the resulting binding domain is
triggered and the amount of light emitted is quantitatively
determined, thereby quantitatively determining the amount of the
analyte of interest present in the sample. Alternatively, the
sample may be contacted with the binding surface prior to
contacting the binding surface with the ECL labeled ligand; the ECL
labeled ligand will then compete with the previously bound analyte
from the sample on the PMAMS surface and displace some of the
previously bound analyte. In an alternative embodiment, the sample
can be treated so as to contain substances/molecules that are
ECL-labeled, and a standard amount of unlabeled analyte of interest
can be contacted with the binding surface prior to or concurrently
with contacting of the binding surface with the sample in order to
carry out a competition assay.
[0338] In a sandwich assay, the ECL labeled ligand is a binding
partner that specifically binds to a second binding moiety on the
analyte of interest. Thus, when analyte that specifically binds to
a binding reagent in a binding domain of a PMAMS is present in a
sample, a "sandwich" is thus formed, consisting of the binding
reagent on the binding domain, bound to analyte from the sample,
bound to the ECL labeled binding partner. In another competitive
sandwich assay, copies of the analyte itself are attached to the
binding domains of the multi-array binding surface prior to
exposure to the sample. Sample is then contacted with the binding
surface. An ECL labeled binding partner (which can specifically
bind to the analyte) will bind the analyte in the absence of free
analyte (from sample) in the assay solution, but will be
competitively inhibited in the presence of free analyte (from
sample) in the assay solution.
[0339] In alternative embodiments, sequential labeling is
performed. For example, in a particular embodiment of a sandwich
assay, the analyte bound to the binding domain is contacted
sequentially with a plurality of ECL labeled binding partners of
the analyte. ECL measurements and optional washing steps are
conducted in between contacting with each different binding
partner. In this way an ECL measurement of a plurality of different
binding moieties of an analyte may be performed (e.g., CD8.sup.+,
a, b T cell antigen receptor positive T cell). Additionally,
multiple ECL labels, each emitting light at a distinguishable
wavelength, may each be linked to a different binding reagent
specific for a different moiety on an analyte. Further, a plurality
of distinguishable reporter means (e.g., ECL label, fluorescent
label and enzyme linked label) each attached to a different binding
reagent specific for a different binding moiety of an analyte may
be used, for example, to distinguish a CD4.sup.+, a, b T cell
antigen receptor-positive cell from a CD8.sup.+ a, b T cell antigen
receptor-positive cell.
[0340] In preferred embodiments the binding domains contain
labelled proteins and/or nucleic acids and/or cells and/or chemical
species. Such labelled components (e.g., ECL labels) may be added
to the binding domain during fabrication, prior to the start of an
assay, during an assay and/or at the end of an assay. For example,
multiple labelled components may be added at various times and
sequential readings may be taken. Such readings may provide
cumulative information. In another embodiment, the binding domains
of the PMAMS may be reused a multiplicity of times. After a given
assay is performed, the surface may be washed under conditions
which rejuvenates the activity of one or more binding domains of
the PMAMS surface. By way of example, some binding reactions may be
reversed by changing the ionic strength of the reaction solution.
Alternatively, heat may be used to disassociate binding complexes.
Some, binding domains may be inherently self-renewing. Binding
domains which contain catalytic (e.g., enzymatic) functionalities
may be utilized more than once. The binding domains are utilized
continuously, and thus can be used in biosensor applications.
[0341] Additionally, the assay may be formatted so that the binding
reagent attached to the multi-array multi-specific patterned
surface is ECL labeled. Upon binding to certain analytes of
interest in a sample, the ECL signal will be quantitatively
modulated. For example, the ECL labeled binding reagent attached to
the surface may be specific for an analyte on a cell surface e.g.,
antigens such as alpha and beta T cell antigen receptor antigens,
or CD4 or CD8 antigens. Upon exposure to a mixture of cells, cells
bound to the surface will sterically hinder the ability of an
electrode surface, brought into proximity with the multi-array
multi-specific surface, from exciting the ECL labeled binding
reagent thus down-modulating the ECL signal.
[0342] Homogeneous and heterogenous assays may be conducted. In
heterogeneous assays, unbound labeled reagent is separated from
bound labeled reagent (e.g., by a washing step) prior to exposure
of the bound or unbound labeled reagent to an electrical potential.
In homogeneous assays, unbound labeled reagent and bound labeled
reagent are exposed to an electrical potential together. In
homogeneous assays, the intensity or spectral characteristics of
the signal emitted by the bound labeled reagent is either greater
than or less than the intensity of the signal emitted by the
unbound labeled reagent. The presence or absence of the respective
bound and unbound components can be determined by measuring the
difference in intensity.
[0343] Once the desired steps of contacting the binding reagents
with analyte or competitor thereof and any binding partners
thereto, have been completed, one then ensures that the ECL label
is subjected to an environment conducive to ECL. Suitable ECL assay
medium are known in the art. Such an assay medium advantageously
includes a molecule that promotes ECL of an ECL label, including
but not limited to oxalate, NADH, and most preferably
tripropylamine. Such a "promoter" molecule can be provided free in
solution, or can be provided by prior linkage to or by production
at (e.g., as a product of a chemical reaction) the PMAMS surface, a
monolayer on the surface, the binding domain, the electrode
surface, a binding reagent, and/or an ECL label, etc. If the medium
surrounding the ECL label bound to the binding domains resulting
from the contacting steps is conducive to ECL, no changes to the
medium need be made. Alternatively, the medium can be adjusted or
replaced to provide a medium conducive to ECL. An electrode and
counterelectrode is already proximate to the binding domain, or is
brought near or in contact with the binding domain, a voltage
waveform is applied, and ECL is detected or measured.
[0344] In a preferred embodiment of the invention, the
above-described steps of contacting the binding reagents with
analyte or competitor thereof and any binding partners thereto, are
carried out in the absence of electrodes and counterelectrodes,
i.e., such that the sample does not contact the electrode or
counterelectrode. Subsequent to these contacting steps, electrodes
and counterelectrodes are brought sufficiently close to the ECL
label bound to the binding domain, to trigger an ECL reaction.
[0345] A support having a PMAMS may be used for sequencing of
nucleic acid strands. For example, a PMAMS with a plurality of
binding domains is prepared with different oligonucleotide probes
of known nucleotide sequence as the binding reagents in different
binding domains. That is, different binding domains will contain
binding reagents of different known nucleotide sequence. The
oligonucleotide chain or fragments of the oligonucleotide chain to
be sequenced are then allowed to bind (hybridize) to the PMAMS
binding domains. The nucleic acids to be sequenced are ECL labeled.
Binding assays are conducted on the PMAMS and the distribution of
ECL signals from the discrete binding domains on the PMAMS is used
to sequence the oligonucleotide chain.
[0346] The above-described method is based on the ability of short
oligonucleotides to hybridize to their complementary or
substantially complementary sequence in another nucleic acid
molecule (see, e.g., Strezoska et al., 1991, Proc. Natl. Acad. Sci.
USA 88: 1089-1093; Bains, 1992, Bio/Technology 10: 757-58, which
are incorporated herein by reference). Conditions can be selected
such that the desired degree of sequence complementarity is
necessary for successful hybridization. Hybridization of a DNA
molecule of unknown sequence to a probe of predetermined sequence
detects the presence of the complementary sequence in the DNA
molecule. The method is preferably practiced such that the
hybridization reaction is carried out with the oligonucleotide
probes bound to the binding domains and the sample DNA in
solution.
[0347] A PMAMS may also be utilized to isolate, screen and/or
select a novel molecule or complex of desired function (e.g.
binding or catalysis). A PMAMS may be used to isolate compounds
and/or lead compounds for therapeutic uses. A PMAMS containing a
plurality of peptides, nucleic acids, viral vectors, or polymers,
synthesized by a variety of combinatorial chemistries, can be made
using the methods of the invention. A wide variety of such PMAMS
treated supports may be used to rapidly screen for binding to, for
example, an ECL labeled cellular receptor. In one method a first
PMAMS with a large diversity of unrelated peptide sequences is used
in order to isolate lead binding peptide sequences. Then a PMAMS
with peptides of related sequences to those which showed binding to
the molecule of interest (e.g., a cellular receptor) on the first
PMAMS are then used. The process is repeated until a peptide with
the desired binding characteristics are found.
[0348] An analyte of interest may be, e.g., a whole cell, a
subcellular particle, virus, prion, viroid, nucleic acid, protein,
antigen, lipoprotein, lipopolysaccharide, lipid, glycoprotein,
carbohydrate moiety, cellulose derivative, antibody or fragment
thereof, peptide, hormone, pharmacological agent, cell or cellular
components, organic compounds, non-biological polymer, synthetic
organic molecule, organo-metallic compounds or an inorganic
molecule present in the sample.
[0349] The sample may be derived from, for example, a solid,
emulsion, suspension, liquid or gas. Furthermore, the sample may be
derived from, for example, body fluids or tissues, water, food,
blood, serum, plasma, urine, feces, tissue, saliva, oils, organic
solvents or air. The sample may comprise a reducing agent or an
oxidizing agent.
[0350] Assays to detect or measure the following substances may be
conducted by the present invention, by incorporation of a binding
reagent specific to said substances into the binding domains of the
binding surfaces of the invention: albumin, alkaline phosphatase,
alt/SGPT, ammonia, amylase, AST/SGOT, bilirubin-total, blood used
nitrogen, calcium, carbon dioxide, chloride, cholesterol-total,
creatinine, GGT, glucose, HDL cholesterol, iron, LDH, magnesium,
phosphorus, potassium, protein-total, sodium, triglycerides, uric
acid, drugs of abuse, hormones, cardiovascular system modulators,
tumor markers, infectious disease antigens, allergy provoking
antigens, immunoproteins, cytokines anemia/metabolic markers,
carbamazepine, digoxin, gentamicin, lithium, phenobarbital,
phenytoin, procainamide, quinidine, theophylline, tobramycin,
valproic acid, vancomycin, amphetamines, antidepressants,
barbiturates, benzodiazepines, cannabinoids, cocaine, LSD,
methadone, methaqualone, opiates, pheneylindine, phropoxyphene,
ethanol, salicylate, acetaminophen, estradiol, progesterone,
testosterone, hCG/bhCG, follicle stimulating hormone, luteinizing
hormone, prolactin, thyroid hormones such as thyroid stimulating
hormone, T4, TUP, total-T3, free-T4, free-T3, cortisol, creatinine
kinase-MB, total-creatinine kinase, PT, APTT/PTT, LD ISOs,
creatinine kinase ISOs, myoglobin, myo light chain, troponin 1,
troponin T, chlamydia, gonorrhea, herpes virus, Lyme disease,
Epstein Barr virus, IgE, Rubella-G, Rubella-M, CMV-G, CMV-M,
toxo-G, toxo-M, HBsAg (hepatitis B virus surface antigen), HIV 1,
HIV 2, anti-HBc, anti-HBs, HCV, anti-HAV IgM, anti-HBc IgM,
anti-HAV, HBeAg, anti-HBeAg, TB, prostate specific antigen, CEA,
AFP, PAP, CA125, CA15-3, CA19-9, b2-microglobulin, hemoglobin, red
blood cells, HBcAb, HTLV, ALT, STS-syphilis, ABO blood type
antigens and other blood typing antigens, cytomegalovirus,
ferritin, B-12, folate, glycalated hemoglobin, amphetamines,
antidepressants and other psychotropic pharmaceuticals.
[0351] Measurements of ECL at different binding domains can be done
sequentially or simultaneously.
[0352] A PMAMS specific for an analyte of interest that is a
cell-surface protein is first exposed to a sample containing cells,
in which it is desired to count the cells in the sample. In a
preferred embodiment, a known sample volume and/or diluted sample
is exposed to a PMAMS which has a multiplicity of binding domains
specific for at least one cell surface antigen. Bound cells can
then be quantified by attachment of a secondary binding group
linked to an ECL tag. This is a group capable of interacting with a
broad range of cell types, for example an ECL-TAG linked to a
hydrophobic group capable of inserting into a cell membrane or to a
lectin directed against cell surface sugars. The ECL-TAG is linked
to a secondary antibody directed against a cell surface antibody.
In a more specific embodiment, several cell types bound to the same
domain can be distinguished by the use of multiple ECL-TAG labeled
secondary antibodies. One preferably ensures that the number of
discrete binding domains specific for a given analyte on the
surface of a cell exceeds the average number of cells that will
bind that are present in the sample. Statistical techniques can
then be utilized to determine the number of cells per sample
volume. This technique can also be used, e.g., to count other
particles such as viruses, where the binding reagent recognizes an
antigen on the virus. The domains can be small compared to the size
of a cell so that only one cell can bind per domain, thus leading
to a digital signal for each domain which can then be analyzed over
the sum of the domains using statistical methods. The domains are
large compared to the size of a cell so that multiple cells can
bind to a domain. In this case, the level of signal from each
domain can be calibrated to give the number of cells per volume of
sample. Image analysis using an array of light detectors (e.g., a
CCD camera or avalanche photodiode array) could be used to count
cells and determine cell morphologies.
[0353] The invention preferably also provides for methods for
conducting ECL reactions, e.g., assays, at a rate of to 1000 ECL
reactions in from 5 to 15 minutes.
5.11. PMAMS for Use with Other Analytic Methods and/or ECL
[0354] The techniques described above for ECL based detection can
be used in conjunction with other assay techniques, e.g., as
domains in which catalyses and other chemical reactions can occur.
Discrete binding domains according to the invention may be used in
other assay techniques such as, clinical chemical chemistry assays,
e.g., electrolyte determinations, clinical enzyme determinations,
blood protein determinations, glucose, urea and creatinine
determinations, and the like. Other assay techniques that may be
combined with ECL assays and/or used alone with the PMAMS of the
invention include chemiluminescent based label, fluorescent based
assays, enzyme-linked assay systems, electrochemical assays (see,
e.g., Hickman et al., 1991, Science 252:688-691) and/or resonance
detection (e.g., surface plasmon and acoustic techniques) assay
systems.
[0355] PMAS supports with drops may be utilized in which there is a
plurality of different chemistries within the array of drops. Each
drop may contain different binding reagents and/or different
chemical assays (i.e., reaction medium for the same). For example,
the drops may be hydrophilic, resting on hydrophilic surface
binding domains which are surrounded by hydrophobic surface
regions. The drops are protected by a hydrophobic solution covering
the surface. The hydrophilic solution to be assayed is deposited on
a second PMAMS with hydrophilic binding domains surrounded by
hydrophobic regions. The two surfaces are brought into registered
proximity so as to bring into contact the hydrophilic domains on
the opposite surfaces and a spectral analysis is performed to
detect reaction products of the chemical assays.
[0356] The fibril mats may be patterned such that there are a
plurality of discrete hydrophobic and/or hydrophilic domains
surrounded by hydrophilic and/or hydrophobic domains. Drops of
aqueous solutions containing binding reagents may rest on
hydrophilic regions and be confined by surrounding hydrophobic
regions. These drops may contain, for example, fibrils, aggregates
of fibrils, binding reagents, ECL reagents, reagents for assays,
surfactants, PEGs, detergents, a plurality of biological molecules
mentioned above by example, and/or combinations thereof.
[0357] The hydrophobic solution covering the first PMAMS is
controllably removed (e.g., evaporated, wicked) so as to expose
only a portion of the hydrophilic drops at the tops to the
environment. A hydrophilic solution to be assayed for an optical
chemical reaction is then exposed to the PMAMS surface--the
hydrophilic micro-drops and the solution to be assayed mix and
analysis (e.g., spectral) is performed.
[0358] PMAMS binding domains may also be used as a pre-filter or
filter. For instance, a cellular specific PMAMS can be used in
certain instances alone as a filter for certain cell types as well
as in conjunction with a size exclusion filter. The resulting
analyte solution is then exposed to a PMAMS specific for
subcellular particulate matter (e.g., viruses). The particulate
subcellular PMAMS and/or a size exclusion filter is used to
generate a small molecule (e.g., protein, small chemical entities)
analyte solution. By utilizing a serial PMAMS assay system the
analyte solution may be sequentially purified in order to decrease
non-specific analyte interactions.
[0359] The optical opacity of a material used for a support,
electrode and/or binding domain may be varied to achieve desired
properties. Such a material may be translucent, transparent or
substantially opaque, depending on the thickness, compositing
and/or optical density of the material.
[0360] The optical opacity of fibril mats increases with increasing
thickness of the mat. Very thin mats are optically translucent.
Thicker mats can be substantially opaque. In some examples, mats
that range in thickness from 0.01 .mu.m to 0.5 .mu.m are
substantially translucent. In other examples, mats with a thickness
greater than 20 .mu.m are substantially opaque. Mats with a
thickness between 0.5 .mu.m and 20 .mu.m have intermediate opacity,
which increases with increasing thickness of the fibril mat. The
optical opacity of a particular thickness of a mat may depend on
the composition, density, derivatization, number of layers, types
and quantities of materials dispersed in the mat, and/or a
combination thereof. It may also depend on the wavelength of the
light used.
[0361] If a material is substantially translucent at a given
thickness and substantially opaque for another thickness, light
emitted from a certain depth in the material may pass out of the
material while light emitted from another (e.g. greater) depth may
be substantially absorbed or scattered by the material. In one
example, the variable opacity of a material allows the material to
be used as an optical filter.
[0362] Light emitted from a certain depth in a fibril mat may pass
substantially through the mat and be observed with a detector
placed on or in proximity to a surface of the fibril mat. Light
emitted from another depth may be substantially absorbed and/or
scattered by the mat and not be observed by a detector placed on or
in proximity to the surface of the mat. This property of a fibril
mat (and/or optically similar materials) may be used to distinguish
between bound and unbound reagents in ECL assay.
[0363] Certain reagents can diffuse (actively or passively), be
pulled (e.g., by suction filtration and/or by capillary action),
wicked, or pushed by pressure to a sufficient depth in a porous
material that emission of light from these reagents is
substantially or entirely absorbed or scattered by the mat. In one
example, a fibril mat acts as both a physical and an optical filter
though which certain reagents are passed, certain reagents are
entrained, and/or certain reagents bind to a very thin layer either
at or in proximity to the surface of the mat. Reagent bound to one
or more binding domains and/or species bound to species bound to
one or more binding domains (these domains being located either on
the surface of the fibril mat or in a very thin layer near the
surface of the mat on the PMAMS) are prevented from diffusing,
being pulled, etc. into or through the mat. Reagents and/or other
solutions are flowed or suspended on and/or over the surface of the
fibril mat such that reagents bind only to a very thin layer on the
surface of the mat. Reagents can be washed through the mats, once
or many times, in one or more directions. Reagents may bind to the
fibril mat, one or more binding domains, other or the same reagents
bound to one or more binding domains, be entrained inside the mat,
pass through the mat, or a combination thereof.
[0364] Porous materials used in supports and/or electrodes may have
more than one layer in which the upper layer has binding domains
and other layers within the mat do not have binding domains. In one
example, a fibril mat, (illustrated schematically in FIG. 29), the
upper layer 2900 is thick enough to prevent passage of light that
originates in layer(s) 2901, 2902 from the mat below this layer.
Light 2903 that originates from sources 2904,2905 bound to this
upper layer can be detected by a detector 2906 located at or in
proximity to the surface of the mat. Light originating from sources
2907, 2908, 2909 in lower layers 2901, 2902 is absorbed and/or
scattered by either or all layers and cannot be detected by the
detectors 2906, 2910.
[0365] A pre-filtration step may be used to select particular
sizes, types, derivatives of fibrils and/or fibril aggregates
before the mat is fabricated. The filter agent used to filter a
suspension of fibrils is a mat of fibrils of a certain or many
porosities.
[0366] A porous material (e.g. a fibril mat) may act as the support
for the binding domains, an electrode which may be used for ECL or
other electrochemical applications, a filter that can be used to
control delivery of reagents, and/or an optical filter that can
transmit, absorb and/or scatter light to varying degrees.
5.12. Electrochromic ECL Display Panels
[0367] The invention also provides for the production of isolated
electrochemical pixels for use in flat panel displays. Lithographic
techniques have been proposed for use in electrochromic and
electrochemiluminescence based flat panel displays to create pixels
which when electronically addressed have limited effect on
neighboring pixels (i.e., limited cross-talk) (see U.S. Pat. No.
5,189,549). A limitation of the lithographic technique for reducing
such cross-talk is that the electrolyte material must be capable of
changing its conductivity upon exposure to light. It is a feature
of the current invention to reduce cross-talk between pixels
without the necessity of using materials capable of photo-induced
conductivity modulation thereby allowing the use of a wide range of
different solutions, gels or films.
[0368] The two electrode surfaces which are the active region of
the pixel are on two surfaces facing each other in a sandwich
configuration. The electrode surfaces are coated with, for example,
complementary electrochromic materials. To reduce cross-talk a
conductive electrolytic film is placed between the electrode
surfaces with non-conductive regions between different electrode
pairs (i.e., between pixel elements). If the coated electrode
surfaces are hydrophilic then the areas of the surface around the
electrodes are made to be hydrophobic (e.g., by means of stamping
or deposition through a mask) and hydrophilic conductive droplets
are placed on the electrode on the first surface (e.g., by means of
a fluidics array) and then the second surface is robotically
aligned and brought into contact with the first surface so that the
electrodes are in register. The electrolytic droplets can thus be
constrained to the area within one pixel without any conductive
material between pixels. The electrode pairs of a pixel are side by
side in close proximity on the same surface. If the coated
electrode pairs are hydrophilic the area encompassing both
electrodes is made to be hydrophilic with a hydrophobic ring around
the hydrophilic electrode area (e.g., by means of stamping or
deposition through a mask). The droplets described in the two
embodiments above are stabilized using hydrophobic solutions. The
viscosity of the solutions may be increased to increase the
stability of the droplet arrays. The hydrophilicity and
hydrophobicity may be reversed. In other embodiments the droplets
may contain solutions capable of polymerizing to increase the
stability and/or conductivity (e.g., conducting polymers) of the
film between or above the electrode pairs. Additionally, structural
features may be utilized to limit cross-talk between pixels. For
example, an elastomeric stamp (e.g., poly(dimethylsiloxane)) with
ring shaped stamp protrusion features capable of circumscribing
side by side electrode pixel pairs on a surface may be used to
isolate electrolytic solutions, gels, or films between pixels.
Alternatively, side by side electrode pixel pairs may be placed in
electrically insulating well-like structures on a surface,
electrolytic solutions, gels or films placed in the wells above the
electrodes, and the entire surface covered or coated to isolate and
contain the electrolytic components of each pixel.
5.13. PMAMS for Use in Other Chemical Reactions
[0369] The PMAMS of the invention can also be used to conduct
chemical reactions not in combination with ECL. For example, all
the techniques and non-ECL assays discussed in Section 5.11 above
can be used.
[0370] A cassette is provided for detecting or measuring an analyte
of interest in a sample, comprising: (a) a first support having a
plurality of discrete binding domains on the surface thereof to
form at least one binding surface, at least some of the discrete
binding domains being of different binding specificities than other
binding domains, each of the plurality of discrete binding domains
being hydrophilic and surrounded by hydrophobic regions, and (b) a
second support having a plurality of hydrophilic domains comprising
reaction media suitable for conducting a chemical assay thereon to
form an assay surface, in which the plurality of discrete binding
domains and the plurality of reaction media is capable of being
brought into contact so that a sample to be analyzed present on
each binding domain is contacted with a reaction medium to detect
or measure an analyte of interest. Alternatively, the binding
domains can be hydrophobic, and the second support has a plurality
of hydrophobic domains containing reaction medium.
[0371] The invention also provides a method for detecting or
measuring analytes of interest in a sample, comprising: (a) placing
drops of a sample containing an analyte to be detected or measured
on a plurality of discrete binding domains on a support surface, in
which the plurality of discrete binding domains comprises at least
one binding domain that contains binding reagents that are
identical to each other and that differ in specificity from the
binding reagents contained within other binding domains, each of
the discrete binding domains being characterized as either
hydrophobic or hydrophilic, with the proviso that the region of the
support surface surrounding each binding domain is (i) hydrophobic
if the binding domain is hydrophilic, and (ii) hydrophilic if the
binding domain is hydrophobic, so as to allow one or more analytes
of interest in the sample to bind to the binding domains, and (b)
contacting the drops on the first support with a surface of a
second support having a plurality of discrete hydrophilic domains
comprising reaction media suitable for conducting a chemical assay
thereon, and (c) determining the presence of the analytes of
interest that are bound to the binding domain.
[0372] Also provided is a method for detecting or measuring
analytes of interest in a sample, comprising (a) placing drops of a
sample containing an analyte to be detected or measured on a
plurality of discrete binding domains on a support surface in which
the plurality of discrete binding domains comprises at least one
binding domain that contains binding reagents that are identical to
each other and that differ in specificity from the binding reagents
contained within other binding domains, each of the discrete
binding domains being characterized as either hydrophobic or
hydrophilic, with the proviso that the region of the support
surface surrounding each of the binding domains is (i) hydrophobic
if the binding domain is hydrophilic, and (ii) hydrophilic if the
binding domain is hydrophobic, so as to allow one or more analytes
of interest in the sample to bind to the binding domains, and (b)
placing drops of a reaction medium on the drops of sample; and (c)
determining the presence of analytes of interest that are bound to
the binding domain.
[0373] In a particular example of this aspect of the invention,
binding domains, each of which have incorporated a different enzyme
that utilizes as a substrate a sequential intermediate in a
chemical reaction are situated on a PMAMS surface, such that the
product of a given enzymatic reaction, which is the reactant for a
subsequent enzyme, flows to the next enzyme in the reaction
pathway. The invention also provides for bulk immobilization of
enzymes on self-assembling monolayers, e.g., for industrial
application, using methods as described above.
[0374] For example, sheets with such immobilized enzymes on one or
both sides may be stacked to achieve high surface area to solution
volume ratios. Alternatively, such immobilized enzymes may be
attached to porous materials. Additionally, such immobilized
enzymes may be on dipsticks, stirring agents, on the walls of tubes
or capillaries, or on the walls of containers such as an incubator
chamber.
[0375] In an alternative aspect of the invention, non-ECL assays
such as described above can be carried out on PMAMS analogs, said
PMAMS analogs differing from PMAMS as described above in that the
PMAMS analogs contain discrete domains for carrying out non-ECL
reactions, the discrete domains not necessarily having incorporated
a binding reagent and therefore not necessarily being binding
domains. Such PMAMS analogs have discrete domains for carrying out
reactions and are prepared so as to inhibit spreading and/or
diffusion of fluid applied to the discrete domains. In one
embodiment, the domains are either hydrophobic or hydrophilic
relative to the surrounding regions on the support surface, in
order to aid in confining the reaction medium and/or sample to the
discrete domains. The use of wells, deposition of reaction medium
or sample on felts or porous materials, deposition and drying of
reaction medium or sample on gels, films, etc., can be used to
inhibit spreading or diffusion. Each of such discrete domains is
less than 1 mm in diameter or width, preferably in the range of 50
nm to 1 mm, most preferably in the range of 1 micron to 1 mm. The
same or different reaction medium can be deposited on each of the
discrete domains prior to sample application, or sample application
can precede deposition of reaction medium.
[0376] In a preferred aspect of the use of PMAMS analogs to conduct
non-ECL assays, drops of reaction medium are placed on a plurality
of discrete domains, preferably delivered concurrently from an
array of microfluidic guides; and then, optionally, to enhance
stability and/or protect the drop, a more viscous solution (e.g.,
oil) is placed on top of the reaction medium or, alternatively, in
between the discrete domain; and then sample containing an analyte
to be detected or measured is applied to each domain, either by
discrete application to each discrete domain or, in bulk, by
exposing the entire surface of the PMAMS analog containing the
domains to a fluid sample. Any resulting reaction in the binding
domains is allowed to proceed, and the results are observed by use
of a reporter and detection system selected from among those known
in the art.
5.14. ECL Assays Employing the Capture of Particles on Porous
Electrodes
[0377] The invention includes a method for performing an
electrochemiluminescence binding assay in which a complex is
formed. The complex includes, at least, a particle and a label
compound capable of electrochemiluminescence. The complex may also
include ligands used in electrochemiluminescence assays as
disclosed for example in Yang H. J. et al., BioTechnology, 12,
(1994), 193-194. The method includes the steps of (a) forming the
complex; (b) collecting the complex by filtration on a porous,
conductive electrode; (c) inducing the label compound in the
collected complex to luminesce by imposing a voltage on the
electrode; and (d) detecting the emitted luminescence from the
electrode.
[0378] In another method for performing an electrochemiluminescence
binding assay, the particle capable of complexing with a component
of an electrochemiluminescence assay is first collected on a porous
conductive electrode. Then the sample containing the analyte of
interest is passed through the porous, conductive electrode and
forms complex on the particle theretofore collected on the
electrode. Then the label compound is induced to luminesce by
imposing a voltage on the electrode and the emitted luminescence is
detected to measure the presence of the analyte of interest. In a
preferred embodiment the porous, conductive electrode will be
pre-prepared with particles incorporated therein and upon use the
sample containing analyte of interest will be passed through the
electrode to form the complex.
[0379] The invention can be adapted to methods for performing a
plurality of electrochemiluminescence binding assays for a
plurality of analytes of interest. In such assays a plurality of
complexes are formed, each of the complexes including at least a
particle and a label compound and these are collected on a
plurality of discrete domains, each of the domains including a
porous conductive electrode. As described, the particles of the
label compound and optionally other assay components may be
complexed in solution then collected on the domains or the domains
may contain the particles in the first instance and be complexed
with the label compound and optionally other assay components by
passing the sample through the electrode.
[0380] The invention can be adapted for use in standard formats for
high-throughput assay processing e.g., 96-well on 384-well
plates.
[0381] In certain preferred embodiments the particles may contain a
luminescence species capable of acting as an internal standard in
the assay. The luminescence thereof can be measured to calibrate
the assay.
[0382] The invention includes binding assays in which particles are
used as solid-phase supports for binding reagents. The term
particle implies no restrictions on the size, shape or composition.
The particles are captured on a porous electrode by filtration and
the presence of analyte is detected by the excitation of ECL from
ECL-labels present in the binding complexes on the particles.
[0383] Particle-based assays have been used in ECL assays (see for
example PCT published applications WO90/05301 and WO92/14139)
assays because they have a high binding capacity. They also allow
the binding event to occur with kinetic rates approaching those
observed for binding events in solution.
[0384] Highly sensitive and precise assays have been conducted
using a system that employs a magnetic field to capture magnetic
particles on a metal surface (see PCT published application
WO92/14139; Deaver, D. R., Nature 377, (1995) 758-760; Yang, H. J.
et al., BioTechnology 12, (1994) 193-194). This capture process
places the particles in close proximity to an electrode so that
excitation of labeled particles can be effected. This technology
has been highly successful in many areas. It does, however, have
some limitations (primarily cost and complexity) that restrict its
use in low cost assays employing disposable cartridges.
[0385] A system that captures particles by filtration through
porous electrodes takes advantage of the high binding capacity and
favorable kinetics of particle-based assays. It also simplifies the
fluidics, may employ a large variety of inexpensive, non-magnetic,
commercially available particles, and can use inexpensive, porous,
carbon-based electrodes. It can also improve the efficiency of ECL
excitation of labels bound to particles. A porous electrode may
have a significantly higher effective surface area than a
non-porous electrode e.g., a metal film. If the electrode is a
fibril mat, which is both porous and comprised of fibrous
materials, the fibrils may contact, e.g. by wrapping around or
laying across, a substantial fraction of the particle.
[0386] The invention includes a cassette containing a porous
electrode that captures particles for the detection of analytes by
ECL. The cassette may contain a working electrode comprising a thin
ECL-active layer of carbon fibrils supported on an ECL-inactive
filter (see Sec. 5.1 and the references cited therein for a
detailed description of carbon fibrils. See Sec. 5.7 for a detailed
description of fibril mats). A separate chamber in the cassette
contains streptavidin-coated particles and dried binding reagents,
e.g. a biotin-labeled capture reagent and an ECL-tag labeled
detection reagent. The cassette also provides a means for
introducing a liquid sample to the chamber containing the
particles, means for capturing the particles on the working
electrode by filtration, a counter electrode and a reference
electrode. The invention also includes associated systems for
conducting ECL assays with the cassette, e.g. a housing, electrical
connections to the electrodes in the cassette, a waveform generator
or potentiostat, a charge coupled device (CCD) for imaging the ECL
emitted from the PMAMS, and a microcomputer for controlling the
waveform generator and analyzing the image received by the
camera.
[0387] There are several desirable embodiments of the working
electrode for particle-based assays in which the particles are
captured by filtration. The material of which the electrode is
formed must be capable of exciting ECL from an ECL label in close
proximity to it when an appropriate electrochemical potential is
applied. If the electrode is porous, the size of the pores must be
large enough to allow filtration of unbound reagents into or
through the electrode but is sufficiently small to capture the
particles.
[0388] Preferably, the working electrode is comprised of a
conducting filter. Conducting filters may be formed, for example,
from porous carbon, aggregate of particulate carbon, from mats of
graphitic fibers, carbon fibrils and/or porous metals that are
capable exciting ECL. The electrode may be composed of a
non-conducting porous material, e.g., a commercially available
polymer-based filtration membrane, coated with an ECL-active
material such as gold, platinum and/or a mat of graphitic fibers).
The electrode may have multiple layers. In one embodiment, a thin
layer of an ECL-active electrode material is deposited on a thicker
ECL-inactive (but electrically conducting) material. The terms
"active" and "inactive" refer to the relative efficacy of the
electrode for exciting ECL from an ECL label, this characteristic
being dependent on both the structure of the ECL label and the
conditions used to trigger ECL in a specific application. The
conductive, ECL-inactive layer ensures good electrical contact
along the entire surface of the active layer, but prevents the
excitation of ECL from unbound ECL-tag labeled reagents that have
filtered through the active layer. In a preferred embodiment, the
ECL-active layer is a thin mat of carbon fibrils and the
ECL-inactive support is stainless steel filter paper.
[0389] Many techniques for immobilization of binding reagents on
particles by either non-covalent and/or covalent coupling reactions
are known in the art. For example, the particles may be coated with
streptavidin and specific binding reagents are then captured using
a streptavidin-biotin interaction.
[0390] A wide variety of particles suitable for use in the
invention are commercially available. These include beads commonly
used in other types of particle-based assays e.g., magnetic,
polypropylene, and latex particles, particles typically used in
solid-phase synthesis e.g., polystyrene and polyacrylamide
particles, and particles typically used in chromato-graphic
applications e.g., silica, alumina, polyacrylamide, polystyrene.
The particle may also be a fiber such as a carbon fibril.
[0391] Materials are available with a variety of functional groups
on their surface. This allows for the use of a wide spectrum of
immobilization chemistries. In some assays, the analyte itself may
act as a particle. For example, an assay for cells with a specific
cell-surface antigen (or an assay to quantify the amount of a
cell-surface marker in a population of cells) may be carried out by
treating the cells with an ECL-tag labeled antibody against the
antigen followed by filtration of the cells onto the porous
electrode.
[0392] This invention may be used to conduct many different binding
assays including those described in section 5.10. These include
immunoassays and nucleic acid hybridization assays in both
competitive and sandwich formats. Many of these assays detect a
labeled analyte or binding reagent in proximity to an electrode.
Conducting the binding reactions on particles in suspension using
gentle mixing if necessary is advantageous because the kinetics of
the binding reactions are particularly favorable (they can approach
those of a homogeneous reaction).
[0393] Alternatively, the particles can be deposited on an
electrode and the binding reactions carried out by flowing samples
past the trapped particles. Particles bearing binding domains can
be deposited on the electrode in a patterned array, i.e. a PMAMS,
by a variety of methods disclosed in Sec. 5.1.
[0394] In one embodiment, the particles are deposited on an
electrode in an array that corresponds to the pattern of a 96-well
plate. This particle/electrode fixture can form the basis of a kit
used for high-throughput ECL assays. A mask with holes in a 96-well
pattern is pressed against the electrode such that the holes in the
mask are aligned with the pattern of deposited particles. The walls
of the holes define the walls of the wells; the electrode and
particles define the bottom of the wells and the binding regions.
Preferred kits may contain any number of holes that meet industry
standards, (e.g. 96 or 384 holes for high throughput
screening).
[0395] Particles bearing binding reagents may be deposited in a
plurality of zones on an electrode. There may be two or more zones
with particles bearing the same binding reagents. There may be two
or more zones with particles bearing different binding
reagents.
[0396] A sample may be delivered to one or more zone by fluidic
guides or it may be flushed through all zones in a single step.
[0397] Alternatively, the particles may be deposited uniformly on
the surface of the electrode, (i.e. not in a patterned array) and a
fixture with holes may be pressed against the electrode to define
the active area of the electrode.
[0398] It is often desirable to include one or more internal
standards. Comparing a signal to one generated by an internal
standard can compensate for variations in the manufacture of an
assay cassette or in the execution of the assay. Dyes may be
incorporated into particles as internal standards. Particles that
incorporate fluorescent dyes are commercially available; some of
these dyes can be induced to emit ECL. A dye that differs from a
specific ECL-label (for example, by its spectral properties, by the
electrochemical potential at which ECL is emitted from it and/or
its ECL lifetime) allows for the simultaneous measurement of ECL
from the specific ECL label and the internal standard. ECL
emissions with different spectral properties can be distinguished
by the use of filters, gratings, and/or other techniques known in
the art for measuring light within a defined spectral window.
[0399] Particles can be used to prepare a PMAMS for the
simultaneous execution of one or more assays for one or more
analytes. By way of example, a plurality of suspensions of
particles can be prepared wherein each suspension comprises
particles bearing immobilized capture reagents. A PMAMS is formed
by applying microdrops of the suspensions, e.g. by methods
disclosed in Sec. 5.1 to defined regions on the working
electrode.
[0400] A cassette may contain only one binding domain for
conducting one ECL assay. In this case, the intensity of the ECL
may be quantified using a single light detector. Comparison of the
light intensity to that obtained from known concentrations of the
analyte allows for quantification of the analyte. Light detection
devices that may be used include photo diodes, photomultiplier
tubes and avalanche photo diodes.
[0401] The cassette may contain a plurality of binding domains. The
emitted light can be imaged to resolve the signals generated at
each binding domain. Imaging may be achieved with an array of light
detectors such as a CCD camera (see Sec. 5.5). Cross talk between
closely packed binding domains can be eliminated by positioning an
array of lenses over the array of binding domains. Alternatively,
mathematical analysis of the intensities measured at the array of
detectors can compensate for such cross talk.
5.15. ECL Assays Employing PMAMS on Electrodes
[0402] The invention includes a cassette containing a PMAMS formed
directly on the surface of an electrode. The cassette contains a
working electrode comprising a thin metal film on a support
material. A plurality of binding domains, i.e. a PMAMS, are present
on the surface of the metal film. The cassette also includes a
means for introducing fluid samples and reagents over the surface
of the electrode, and a counter electrode to allow for
electrochemical excitation of ECL at the working electrode. A
reference electrode may also be included for better control of the
electrochemical potential at the working electrode. An apparatus
for conducting ECL assays including a cassette which may comprise a
housing, electrical connections to the electrodes in the cassette,
a waveform generator or potentiostat, a CCD camera for imaging the
ECL emitted from the PMAMS, and a microcomputer for controlling the
waveform generator and analyzing the image received by the
camera.
[0403] The formation of PMAMS directly on the working electrode has
several advantages over previous ECL systems: The combination of
the working electrode and the solid phase support for the binding
assays into one unit greatly simplifies the manufacture and
execution of ECL assays in a disposable format, allowing disposable
assays to be produced at lower cost. A plurality of assays can be
performed without the use of multiple ECL labels. The excitation of
ECL from each of a plurality of assays can be conducted
simultaneously by applying a potential to one working/counter
electrode pair, all of the binding domains being located on the
surface of the same working electrode). The use of the surface of a
metal as the support for the PMAMS allows the use of well developed
technology--e.g., the formation and patterning of self-assembled
monolayers (SAMs) on metals--for the formation of the PMAMS.
[0404] The working electrode may be made of a wide range of
materials including metals (e.g., gold and platinum), metal oxide
conductors and semiconductors (e.g., ITO), carbon (e.g., graphite,
carbon black, carbon fibrils), and conducting organic polymers
(e.g., polythiophene). The electrode may comprise a composite of
different materials.
[0405] In one embodiment, the working electrode is a thin (5
nm-10,000 nm) film on a substrate. The preparation of such films by
techniques including evaporation, polymerization, sputtering,
chemical vapor deposition, and plating is known in the art. In a
preferred embodiment, the working electrode is a thin film of gold
evaporated on a substrate. The properties of the substrates for the
thin film electrodes can be chosen according to the requirements of
the assay system. The substrate may be solid, or if filtration of
samples through the electrode or wicking of samples along the
electrode is desired, the substrate may be a porous material e.g.,
a filtration membrane.
[0406] Binding reagents may be immobilized by non-specific
adsorption directly to the electrode surface or by covalent
attachment to a chemical functional groups on the surface of the
electrode. One approach to the introduction of chemical functional
groups on the surface of an electrode is electrodeposition or
electropolymerization of thin films. Another approach is the
preparation of self-assembled monolayers (SAMs). Examples of SAMs
that can be prepared on electrode materials include monolayers of
organic thiols on gold, and organic silanes on ITO (see Sec. 5.1).
As shown in FIG. 50, a SAM may be prepared by the reaction of a
molecule A-L-B 5032 with the surface of the electrode 5033, where A
is the functional group responsible for the attachment of the
molecule to the electrode, L is a linking chain, and B is a
functional group which can be used for the attachment of binding
reagents 5034 to the surface. Alternatively, B may be a binding
reagent.
[0407] In a preferred embodiment, the SAM is formed by the reaction
of terminally functionalized alkane thiols
(HS--(CH.sub.2).sub.n--B) with thin films of gold deposited on a
substrate. Alkane thiols with a variety of functional groups (B)
can be prepared, allowing for the use of a variety of
immobilization chemistries. For example, if group B includes a
carboxylate group, binding reagents which include an amino group
can be immobilized by reaction with the SAM after activation of the
SAM with ethyl-3-diaminopropylcarbodiimide (EDC) in the presence of
(N-hydroxysuccinimide (NHS). Alternatively, functional group B may
be a methyl group, binding reagents may be immobilized by
non-specific hydrophobic interactions or if functional group B
contains a biotin moiety, streptavidin or other reagents linked to
streptavidin either covalently or through a biotin-streptavidin
interaction) may be immobilized on the surface.
[0408] Many other chemistries for the immobilization of binding
reagents are known in the art and can be employed. In some cases it
may be desirable to control the density of functional groups B on
the surface of the electrode in order to control the density of
binding reagents immobilized on the surface or to maintain some
desirable property of the surface, e.g. resistance to non-specific
binding. The control of the surface density of the functional group
B can be achieved by treating the electrode surface with a mixture
containing the monomers A-L-B and A-L-C in a ratio determined to
produce a mixed SAM with the desired concentration of B on the
surface. The functional group C is chosen to be resistant to the
immobilization chemistry used to couple binding reagents to B and
may have other desirable properties such as producing surfaces with
reduced non-specific binding.
[0409] The formation of PMAMS on the surface of an electrode can be
achieved by a variety of methods including: (i) photo-lithographic
immobilization; (ii) microcontact printing; and (iii) the
controlled application of drops of binding reagents to the surface
through the use of microcapillary arrays or ink-jet printing (see
discussion in Sec. 5.1). Patterned SAMs can be used to better
define the areas on the surface which are modified with binding
domains. For example, microcontact printing can be used to pattern
an area of circles on a gold surface presenting a hydrophilic SAM
formed from a carboxylic acid terminated alkane thiol. The
remaining gold surface can then be reacted with a methyl terminated
alkane thiol to give a hydrophobic SAM. After activation of the
surface with EDC in the presence of NHS, drops, each containing a
different antibody, are applied to the hydrophilic circles. The
drops will be confined to the hydrophobic regions due to the
hydrophobic nature of the surface outside the circles, thus
allowing careful control of the area of the immobilized binding
domains.
[0410] The types of assays which can be conducted using PMAMS
immobilized on a electrode include those described in Sec. 5.10.
Many of these assays (for example, immunoassays and nucleic acid
hybridization assays in both competitive and sandwich formats) rely
on the detection of the binding to the electrode surface of a
binding reagent or analyte that has been labeled with an ECL-active
group (tag). The intensity of the signal emitted from a tag-labeled
reagent on the surface of SAM can be strongly influenced by the
nature of the potential waveform used to excite ECL. For example,
SAMs of alkanethiolates on gold are good electrical insulators but
highly oxidizing or reducing potentials at the electrode surface
may reduce the insulating properties of the film by introducing
disorder in the monolayer. Excitation of ECL at potentials which do
not introduce disorder into the SAM requires the transfer of
electrons through the monolayer by tunneling. Much higher intensity
signals can be achieved by applying potentials that introduce
disorder into the SAM, thus allowing less hindered flow of current
to the electrode. These potentials can be applied prior to or
during the excitation of ECL. Alternatively, the SAMs could be
formed using conditions known in the art to give disordered
monolayers. The conductivity of monolayers can also be increased by
including a constituent in the monolayer which facilitates the
transfer of electrons (for example, by the introduction of a
pi-conjugated system into the linking group L). The formation of
SAMs with high conductivity is discussed in more detail in section
5.7.
[0411] In some cases the use of potentials which do not introduce
disorder into the SAMs is advantageous. Under these conditions, the
discrimination of bound tag-labeled reagents from unbound
tag-labeled reagents in solution will be maximized due to the
strong dependence of electron tunneling on distance, thus,
eliminating the need for a wash step. An ECL label on the surface
will give a much stronger ECL signal than an ECL label in solution)
ECL can be modulated by changes in conductivity between the SAM and
the ECL label that result from a binding event. The use of this
approach to conduct nucleic acid hybridization assays is described
in Sec. 5.7.
[0412] A cassette of the invention may contain only one binding
domain for conducting one ECL assay. The intensity of the ECL may
be quantified using a single light detector. Comparison of the
light intensity to that obtained from known concentrations of the
analyte allows for quantification of the analyte. Light detection
devices which may be used include photo diodes, photomultiplier
tubes and avalanche photo diodes. A cassette may also contain a
plurality of binding domains. The emitted light from such cassette
must be imaged to separate the signals generated at each binding
domain. Imaging may be achieved by an array of light detectors such
as a CCD camera (see Sec. 5.5). Cross talk between closely packed
binding domains can be eliminated by positioning an array of lenses
over the array of binding domains or by mathematical analysis of
the intensities of the signals from the several binding
domains.
5.16. ECL Assays Employing PMAMS on a Porous Substrate
[0413] FIG. 37 shows a cassette where binding domains 3702 in
and/or on a matrix 3703 are presented on a surface 3701. After
completion of binding reactions on the binding domains, a second
surface 3700 supporting a working electrode 3704 and a counter
electrode 3705 is positioned so that the binding domains are in
close proximity to the working electrode. Luminescence from an ECL
label bound to the binding domains may be detected from either or
both surfaces. We refer to this configuration for ECL as the "Two
Surface" ECL assay.
[0414] FIG. 38 shows a cassette where binding domains 3805, 3806,
3807 are presented on the surfaces of matrices supported on a
counter electrode 3800. After completion of binding reactions on
the binding domains, a working electrode 3801 is positioned in
close proximity to the surface of the matrices. Luminescence from
an ECL label bound to a binding domain may be detected through
either or both of the electrodes if either or both of the
electrodes is transparent or semi-transparent and/or from the
side.
[0415] The invention also includes an apparatus for conducting ECL
assays using cassettes containing a PMAMS. An apparatus for
conducting ECL assays using the cassette described in FIG. 38
includes means for making electrical connections to the electrodes,
means for controlling the potential at the electrodes, means for
moving the matrix into close proximity with the working electrode
and means for imaging the light emitted during excitation of
ECL.
[0416] The Two Surface method has several advantages over previous
ECL methods. A plurality of assays can be performed conveniently
without the use of multiple ECL labels. The excitation of ECL from
each of a plurality of assays can be conducted simultaneously by
applying a potential to one working/counter electrode pair, all the
binding domains being placed in proximity to the same working
electrode. The working electrode can be protected during the
binding reaction from the sample by a physical barrier that is
removed prior to the excitation of ECL, thus, preventing
contamination of the electrode surface which could result in a
change in its electrochemical performance. As illustrated in FIG.
55 for the case of a sandwich immunoassay, the binding of ECL-tag
labeled reagent 5203 to analyte 5202 bound to primary antibody 5201
immobilized on the matrix 5200 results in the optimal presentation
of the tag 5204 to the electrode surface 5205, (i.e. with a minimum
of organic material--such as protein, nucleic acid, or linking
groups--between the tag and the surface of the electrode. The
matrix may be used for the concentration and/or separation of
components of a sample, for example, by electrophoresis and/or
filtration through the matrix. The matrix may be used as a medium
for the storage of assay reagents in dried or partially hydrated
form. The surface of the matrix can be placed in conformal contact
with the working electrode.
[0417] The PMAMS are preferably formed in and/or on a matrix with
one or both of the following characteristics. The matrix is capable
of carrying ionic currents between the working and counter
electrodes, and therefore, can complete the electrochemical
circuit. The matrix is preferably capable of making intimate
contact with the working electrode e.g. it is elastomeric and/or
compliant. Materials with these characteristics are known in the
art and include porous materials such as filtration membranes and
water-swollen polymeric gels. In some embodiments of the invention,
e.g. if light excited at the working electrode is detected through
the matrix, it is advantageous for the matrix to be
transparent.
[0418] PMAMS can be generated on porous materials (e.g., gels) with
varying pore size and solvent content. For example, polyacrylamide
gels varying in pore size can be made by varying the concentration
of acrylamide and the degree of crosslinking.
[0419] On such matrices with pore sizes smaller than the analyte,
binding reactions will occur substantially on the surface of the
gel. In this case, filtration and/or electrophoresis through the
gel can be used to concentrate analytes at the surface of the gel
and modulate the kinetics, e.g., increase the rate, of the binding
reaction. Faster kinetics are advantageous in rapid assays and may
generate increased sensitivity in a shorter time period.
[0420] On matrices with pore sizes larger than the analyte, binding
reactions can occur on the surface as well as the bulk of the gel.
In this case, filtration and/or electrophoresis can be used to
increase the kinetics of binding as well as to remove unbound
species from the surface.
[0421] PMAMS formed on gels can be stored wet and/or they may be
stored in a dried state and reconstituted during the assay. The
reagents necessary for ECL assays can be incorporated in the gel
before storage, by permeation into the gel or by incorporation
during formation of the gel, and/or they can be added during the
assay.
[0422] The immobilization of binding domains to matrices by
covalent and noncovalent linkages is known in the art. Some
examples of methods for the immobilization of binding domains to a
variety of matrix materials is described in more detail in Sec.
5.1. Sec. 5.1 also describes in detail methods for the patterning
of binding domains on a matrix to form a PMAMS. These patterning
methods may include the following: i) photolitho-graphic
immobilization; ii) patterned application of microdrops of reagents
to the surface of a matrix; iii) application of drops or microdrops
containing the binding domains in the matrix in liquid form to a
substrate followed by solidification and/or gelling of the liquid
using known techniques including, crosslinking, polymerization,
cooling below the gelling transition, etc., to give distinct drops
on the substrate composed of the matrix material, each solidified
drop thereby comprising a different binding domain; iv) using
matrices to achieve separations, e.g. by electrophoresis in a
polyacrylamide slab; and v) Forming a layered structure of matrices
each containing one or more binding domains.
[0423] The working electrode is preferably made from an electrode
material that is capable of exciting ECL from an ECL label in close
proximity to the surface when the appropriate electrochemical
potential is applied. In some embodiments light is detected from
the surface of the PMAMS through the working and/or the counter
electrode. In these cases, it is advantageous to use a transparent
or semi-transparent electrode material. These electrode materials
are known in the art. Examples include films made of indium tin
oxide as well as very thin (<30 nm) films of gold.
Alternatively, it may be advantageous to protect the working
electrode from the sample. A physical barrier on the electrode may
protect it during incubation of the sample with the PMAMS. The
physical barrier is then removed before placing the PMAMS in close
proximity to the electrode.
5.17. ECL Assays Employing PMAMS on Composite Electrodes
[0424] In preferred embodiments of the invention the electrode is a
composite of a polymer containing a multiplicity of carbon fibrils
dispersed therein. Desirably the composite is porous.
[0425] A preferred apparatus for conducting an assay comprises as a
first element a matrix containing carbon fibrils dispersed therein,
and one or more binding domains containing a reagent capable of
binding a component of an assay.
[0426] An apparatus for detection of an analyte by
electrochemiluminescence may comprise an electrode comprised of a
composite of a matrix having a multiplicity of conducting particles
dispersed therein and a binding domain containing a reagent capable
of binding a component of an electrochemiluminescence assay.
Desirably the matrix is a polymer and the conducting particles are
carbon. The conducting particles are desirably are carbon fibers
and best results obtained were the carbon fibers or carbon
fibrils.
[0427] Apparatus for use in the detection of a plurality of
analytes are also included in the invention. In such apparatus the
electrode is comprised of a matrix containing a multiplicity of
conducting particles dispersed therein and the plurality of binding
domains supported on a surface of the electrode, each of those
domains containing the reagent capable of binding a component of an
electrochemiluminescence assay.
[0428] The properties of electrodes comprising a polymer and
dispersed carbon fibrils may be modified by a subjecting the
composite to various chemical and physical steps such as oxidation,
exposure to a plasma and exposure to a reagent capable of
derivatizing the electrode by addition of one or more functional
groups. In the latter method the polymer can be derivatized or the
fibrils contained therein can be derivatized or both can be
derivatized. Desirably the composite is subjected to a chemical or
physical treatment to affect the modification for a time sufficient
to alter the electrical potential at which electrochemiluminescence
occurs in an electrochemiluminescent compound situated at said
composite. It is also within the invention to modify the properties
of any electrode comprising a polymer and multiplicity of carbon
fibrils dispersed therein by modifying the electrode to expose a
desired functional group thereupon. The invention also includes
electrodes which have been modified by chemical or physical
treatment to alter the electrical potential at which
electrochemiluminescence occurs.
[0429] The invention includes a cassette containing a PMAMS formed
directly on the surface of an electrode comprised of more than one
material, i.e. a composite electrode. The several components of
such a cassette are described above.
[0430] The composite electrode may be comprised of conductive
and/or electrochemically active particles impregnated in a support
matrix. For example, the matrix may be comprised of oils, waxes,
paraffins, plastics, ceramics, teflon, polymers, elastomers, gels
and/or combinations thereof. Some examples of commercial polymers
that can be used in the manufacture of composite electrodes
include, but are not limited to, EVA, polyethylene (PE),
polystyrene (PS), and ABS.
[0431] The matrix can be chosen to meet design requirements for a
given application. The material may be appropriate for a specific
type of immobilization chemistry, it may give high specific signal
and/or low background signals in a particular type of assay, and/or
because the material has desirable physical properties, e.g.,
flexibility, strength, chemical resistance.
[0432] A composite electrode can be formed using any particles that
when combined in a matrix provides an electrically conductive
composite. The particles may be carbon, e.g. particulate carbon,
carbon black, carbon fibers, carbon felts and preferably are carbon
fibrils (Secs. 5.1 and 5.7).
[0433] Composites that contain more than one type of particle
and/or more than one type of material for the matrix can be used.
For example, a composite electrode may include one type of particle
to impart electrical conductivity and ECL-activity and another type
of particle as a support for binding domains.
[0434] In a preferred embodiment, a composite electrode is
comprised of a blend of carbon particles and a matrix. In a
particularly preferred embodiment, a composite electrode is
comprised of carbon fibrils and a polymer. U.S. Pat. Nos. 5,304,326
and 5,098,771 describe polymer composites impregnated with
fibrils.
[0435] Fibril-polymer composite electrodes can be produced by
techniques known in the art of manufacturing plastic materials and
parts. For example, flat electrodes can be cut from pressed sheets
or extruded films of a fibril composite. Electrodes with
complicated shapes or surface features such as grooves or channels
for the movement of fluid or wells for reaction chambers can be
formed by injection molding.
[0436] The composite electrode may be a solid or may be porous.
Porous composites may be formed by using techniques for producing
porous plastic materials, e.g., filtration membranes. Filtration
through a porous composite electrode can improve the kinetics of
binding reactions to binding domains immobilized on the surface of
the electrode.
[0437] Binding reagents may be immobilized on unmodified composite
electrodes. For example, binding reagents may be immobilized by
non-specific adsorption onto the matrix and/or onto the conductive
particles. Functional groups present on the matrix and/or the
conductive particle can be used for immobilization of reagents.
These reagents can serve as binding reagents and/or as reagents
that change the properties of the surface e.g. wettability or
resistance to non-specific binding. Methods for covalent and
non-covalent immobilization of reagents on materials that can be
used as matrices are known in the art (see Sec. 5.1).
[0438] In one embodiment, the carbon particles comprise between
0.1% and 99.9% by weight of the composite. In another embodiment
the carbon particles comprise between 0.5% and 50% by weight of the
composite. In a preferred embodiment, the carbon particles comprise
between 1% and 30% by weight of the composite. In a particularly
preferred embodiment, the carbon particles comprise between 2% and
20% by weight of the composite.
[0439] The use of carbon fibrils in composites can be particularly
advantageous. The conductivity and high aspect ratio of fibrils may
allow preparation of composites that have high conductivity at low
weight-percentage of carbon in the composite (when compared to
composites containing carbon particles other than fibrils, present
at the same weight-percentage). Composites with low carbon loading
that still have high conductivity can be advantageous, since high
carbon loadings of some carbon particles can compromise the
structural integrity and/or processability of composites.
Composites containing carbon fibrils can also have high binding
capacities due to their large exterior surface area. Processing of
the composite to expose fibrils (e.g. by chemical means or by
exposure to a plasma) can alter the binding capacity,
advantageously, to increase it. (By binding capacity here we mean
the amount of a reagent that can be immobilized on a given
geometric area of a material, e.g. nanograms of protein per
cm.sup.2 of material. By geometric area we mean the area of a
material defined by the dimensions of the material (e.g. a square
piece of material with dimensions of 1 cm.times.1 cm has a
geometric area of 1 cm.sup.2)). One of the limitations of many
materials is that the binding capacity is limited by the geometric
area of the material. For example, if a smooth, flat surface is
used (e.g. the surface of a metal), it may not be possible to
obtain a binding capacity of a reagent (e.g. a protein, nucleic
acid, a binding reagent) that exceeds that of a close-packed
monolayer of said reagent distributed over the geometric area of
the smooth flat surface. Use of composites with exposed fibrils
overcomes this limitation. Exposure of fibrils creates a plurality
of protruding fibrils (each having high surface area) at the
surface of the composite: the total surface area of fibrils
available for binding of reagents can significantly exceed the
geometric area of the composite. In one embodiment, the binding
capacity for a reagent on such a composite can be greater than 1
times that of a close packed monolayer of said reagent distributed
over the geometric area of said composite. In another embodiment,
the binding capacity for a reagent on such a composite can be
greater than 2 times that of a close packed monolayer of said
reagent distributed over the geometric area of said composite. In a
preferred embodiment, the binding capacity for a reagent on such a
composite can be greater than 10 times that of a close packed
monolayer of said reagent distributed over the geometric area of
said composite. In another preferred embodiment, the binding
capacity for a reagent on such a composite can be greater than 100
times that of a close packed monolayer of said reagent distributed
over the geometric area of said composite.
[0440] In some embodiments, composites containing carbon fibrils
can be resistant to damage by certain solvents, temperatures,
reagents and processes that might otherwise damage the matrix of
the composite (if the matrix alone were treated). This resistance
to damage can be advantageous in processing. For example, it may be
possible to use certain procedures for derivatization of the
composites (e.g. a procedure that requires a solvent that dissolves
the matrix alone, but does not appreciably dissolve the matrix or
fibrils when they are present together as a composite).
[0441] The composite electrode may be modified by chemical or
mechanical treatment to improve the immobilization of binding
reagents. The surface may be treated to introduce functional groups
for immobilization of reagents. Techniques that may be used include
exposure to electromagnetic radiation, ionizing radiation, plasmas
or chemical reagents such as oxidizing agents, electrophiles,
nucleophiles, reducing agents, strong acids, and strong bases
and/or combinations thereof (see Sec. 5.18).
[0442] One particularly interesting embodiment is the modification
of such composite electrode, and more broadly a composite material
(not limited to an electrode) comprising a matrix (such as a
polymer) and one or more fibrils and/or fibril structures dispersed
therein, by treatment with a plasma. The treatment is carried out
in order to alter the surface characteristics of the fibrils,
fibril structures and/or the matrix, which come in contact with the
plasma during treatment; by this means the fibril composite treated
can be functionalized or otherwise altered as desired. Once
equipped with the teaching herein, one of ordinary skill in the art
will be able to adapt and utilize well-known plasma treatment
technology (without the need for further invention or undue
experimentation) to the treatment of such composite materials.
Thus, the treatment can be carried out in a suitable reaction
vessel at suitable pressures and other conditions and for suitable
duration, to generate the plasma, contact it with the composite
material, and effect the desired kind and degree of modification.
Plasmas such as those based on oxygen, ammonia, helium or other
chemically active or inert gases can be utilized. Depending on its
properties, the modified composition can be utilized as an
electrode (such as described above) or for other applications.
[0443] Examples of other gases used to generate plasmas include
argon, water, nitrogen, ethylene, carbon tetrafluoride,
sulfurhexafluoride, perfluoroethylene, fluoroform,
difluoro-dicholoromethane, bromo-trifluoromethane,
chlorotrifluoromethane, and the like. Plasmas may be generated from
a single gas or a mixture or two or more gases. It may be
advantageous to expose a composite material to more than one type
of plasma. It may also be advantageous to expose a composite
material to a plasma multiple times in succession; the conditions
used to generate the plasma, the duration of such successive
treatments and the duration of time between such successive
treatments can be varied to accomplish certain alterations in the
material. It is also possible to treat the composite material (e.g.
coat the material with a substance, wash the surface of the
material, etc.) between successive treatments.
[0444] Plasma treatment of a composite material may effect several
changes. For example, a composite material comprising a polymer and
a plurality of carbon fibrils dispersed therein can be exposed to
plasma. Exposure to plasma may etch the polymer and expose carbon
fibrils at the surface of the composite, thus increasing the
surface area of exposed carbon fibrils (e.g. so that the surface
area of the exposed fibrils is greater than the geometric surface
area of the composite). Exposure to plasma may introduce chemical
functional groups on the fibrils or the polymer; these functional
groups may be used for the immobilization of reagents.
[0445] Plasma may be used to bond reagents to the composite
material. For example, the composite material may be exposed to a
solution containing a reagent (e.g. a detergent, a polyaromatic
molecule, a hydrophobic molecule, a charged molecule, and the like)
so that some amount of the reagent coats the composite material.
The reagent-coated composite material can then be exposed to
plasma; exposure to the plasma bonds the reagent to the composite
material. In another example, a composite material coated with a
biomolecule (e.g. a protein, nucleic acid or the like) is exposed
to plasma: exposure to the plasma bonds the biomolecule to the
composite material. In another example, a composite material is
coated with a reagent that binds one or more desired reagents
specifically (e.g. an affinity chromatography resin, a polymer with
biospecific ligands) and exposed to plasma. Exposure to plasma
bonds said reagent to the composite material.
[0446] Reagents bound to composite materials can be used to
immobilize other reagents on the composite. For example, a
hydrophobic reagent bonded to composite materials may enhance
adsorption of proteins to the composite. Affinity chromatography
resins, biospecific polymers, proteins and the like may enhance
immobilization of biomolecules to the composite materials (e.g.
biospecifically and/or non-specifically).
[0447] Plasma can also be used to induce polymerization of reagents
on composite materials. The products from plasma induced
polymerization can then be used to immobilize reagents on composite
materials. For example, monomeric precursors can be coated on
composite materials; exposure to plasma may induce grafting and/or
polymerization of some or all of said monomeric precursors. In
another example, a polymer can be coated on a composite material by
treating the composite with a plasma comprising the monomer. In
another example, a composite material can be coated with monomer or
polymer by exposing the composite to a plasma so that
polymerization initiating species are generated on the composite,
and then treating said composite with a monomer.
[0448] It may be advantageous to immobilize binding reagents on
both the matrix and the particles or it may be advantageous to
immobilize binding reagents on only one of the components, i.e. the
matrix or the particles. By way of example, a composite electrode
comprised of fibrils in EVA (a copolymer or ethylene and vinyl
acetate) may be treated with a mixture of chromic acid and sulfuric
acid to introduce carboxylic acid groups on the electrode. These
carboxylic acid groups can then be used to immobilize binding
reagents containing amines by formation of an amide bond.
Alternatively, a composite of fibrils in EVA can be treated with
sodium hydroxide. In this case, the fibrils remain unmodified but
hydroxyl groups are exposed on the polymer. These hydroxide groups
can then be used to immobilize binding reagents containing a
nucleophile.
[0449] Modification of composites may lead to other favorable
properties. Modification of the matrix and/or the particles may
produce a composite electrode with a high binding capacity. The
introduction of hydrophilic groups to the composite electrode may
hydrate the matrix and lead to the formation of a thin
water-swollen gel layer. Reagents can be immobilized within such a
gel layer, allowing for the immobilization of more reagents than
could occupy a flat, solid, surface with the same geometric surface
area. Partial degradation of the matrix can increase the exposed
surface area of the conducting particles and lead to high
surface-area electrodes for the immobilization of binding reagents
directly on the conductive particles, especially when the particles
are fibers which can extend into the solution.
[0450] Modification of a composite surface may shift the
electrochemical potential required to excite ECL. Modification of
the composite electrode may reduce or increase the overpotential
required for excitation of ECL from an ECL tag, thereby allowing
certain signals, e.g. the signal from an analyte and a background
signal, to be resolved.
[0451] The formation of PMAMS on the surface of a composite
electrode can be achieved by a variety of methods including
photolithographic immobilization, microcontact printing and/or the
controlled application of drops of binding reagents to the surface
through the use of microcapillary arrays or ink-jet printing (see
Sec. 5.1). Alternatively, the surface of a composite electrode may
be divided into distinct regions by placing it in contact with a
mask.
[0452] The invention includes a disposable multiwell plate for use
in ECL assays (hereon referred to as an "ECL Plate"). In one
embodiment, an ECL Plate is manufactured by shaping (e.g.,
pressing, molding, or forming) a conductive composite into the form
of a multiwell microtiter plate. In another embodiment, a mask is
formed that comprises an array of holes through a sheet of a
material. Such a mask is then sealed against an electrode (the
electrode is preferably a conducting composite or a fibril mat; the
preparation of fibril mats is described in detail in Section 5.7,
Section 5.18 and the references therein). The holes through the
mask will then define wells with walls comprising the mask and
bottom comprising the electrode. The mask and the electrode may be
provided to the user as a preassembled disposable cassette, or as
individual disposable components of a kit. Alternatively, only the
electrode may be disposable. The electrode may be solid and/or
porous. In the case of a porous electrode, binding reactions may be
carried out by filtering reagents through the electrode (multiwell
filtration manifolds for use in binding assays--"dot blots"--are
known in the art). In a different embodiment of the ECL Plate, a
plurality of holes in a mask (as described in the previous
embodiment) is sealed against a plurality of individual electrodes
such that the electrodes in individual wells and/or groups of wells
can be individually probed.
[0453] An ECL plate is preferable shaped in a standard form used
for multiwell microtiter plates. These standard formats are known
in the art and include, but are not limited to, 24, 96, and 384
well plates. The use of a standard format allows the integration of
commercially available equipment for carrying out binding reactions
on microtiter plates (e.g., equipment for moving plates, washing
plates and/or dispensing samples). The invention includes an
apparatus for exciting ECL from the electrode or electrodes of an
ECL Plate and quantifying the ECL emitted from each well.
[0454] ECL plates may be provided to the end user with immobilized
binding reagents for one or more analytes. Alternatively, the user
could be provided with a kit comprising an ECL Plate and the
reagents necessary for immobilizing binding reagents (when such
binding reagents are provided by the user).
[0455] Composite electrodes may be used in assays that do not use
ECL. They may be used as solid-phase binding supports for assays
based on fluorescence, chemiluminescence, or ELISA-type formats.
They may be used as electrodes and/or solid phase supports for
assays based on amperometric or potentiometric electrochemical
detection.
5.18. ECL Assays Employing PMAMS on a Porous Electrode
[0456] The electrode of the invention may comprise a mat of a
multiplicity of carbon fibrils. Such mats have now been found to
perform well as electrodes for use in electrochemiluminescence
assays.
[0457] The mats broadly comprise a multiplicity of carbon fibrils
and at least one domain containing an assay reagent. In one
embodiment of the invention the mat may be comprised of two or more
layers of different conductivity, two or more layers of derivitized
or underivitized carbon fibrils or combinations of derivitized and
underivitized fibrils, two or more layers of fibrils of different
optical opacity or two or more layers of fibrils of different pore
sizes.
[0458] Desirably these mats are used in electrodes for
electrochemiluminescence assays. The electrode includes a support
and a fibril mat comprising a multiplicity of carbon fibrils and
means for making electrical contact with the mat. The electrode may
contain a binding domain containing a reagent capable of binding a
component of an electrochemiluminescence assay.
[0459] The invention includes kits for making electrodes for use in
such assays. The kits include a support, a fibril mat and means for
making electrical contact with the mat. The fibril mat may include
a binding domain.
[0460] The electrode may be conductive or porous and desirably is
conductive and porous and may be, for example, comprised of a
metal-coated porous material. The electrode may be stainless steel
fiber mesh.
[0461] Fibril mats for use as a support for an electrode in an
electrochemiluminescence assay may be prepared in several different
ways. In one such method the fibrils are produced with a binding
reagent immobilized on their surface. These fibrils are dispersed
in a medium. They are thereafter filtered from solution to produce
a fibril mat.
[0462] Alternatively, the fibril mat may be prepared by dispersing
the fibrils in a medium, filtering the fibrils from the medium to
prepare the mat and finally derivatizing the fibril mat to prepare
them for mobilization of a binding reagent thereupon.
[0463] The invention broadly includes methods for performing an
electrochemiluminescence binding assay for an analyte of interest.
The method includes the steps of (a) an electrode comprised of a
conductive polymer; and (b) a binding domain containing a reagent
capable of binding a component of a binding
electrochemiluminescence assay.
[0464] The method of the invention can be used to conduct
electrochemiluminescence binding assays for a plurality of analytes
of interest in a biological sample. This method includes the steps
of (a) contacting a sample containing analyte of interest and a
label compound capable of electrochemiluminescence, with an
electrode comprising a multiplicity of carbon fibrils containing a
binding domain containing a reagent capable of binding a component
of an electrochemiluminescence assay; (b) inducing the label
compound at the electrode to luminesce by imposing a voltage
thereupon; and (c) detecting the emitted luminescence.
[0465] Alternatively, the method includes (a) contacting a sample
containing a plurality of analytes of interest and a label compound
capable of electrochemiluminescence with a plurality of electrode
zones, each of which comprises a fibril mat containing a domain
containing a reagent capable of binding a component of an
electrochemiluminescence assay; (b) inducing the label compound
collected on said fibril mats to electrochemiluminescence; and (c)
measuring the emitted luminescence.
[0466] The invention also includes a cassette containing a porous
electrode. The cassette contains a working electrode consisting of
a porous mat of carbon fibrils supported by a porous material. One
or more binding domains are present on the surface of the working
electrode.
[0467] The porous electrode may be comprised of carbon e.g.,
graphitic carbon, glassy carbon or carbon fibers and in a
particularly preferred embodiment comprises carbon fibrils. The
binding domains of the PMAMS may be supported by a fibril mat (see
Sec. 5.7). The mats may support a plurality of discrete binding
domains, any two or more of which may be identical to each other or
all of which may differ from one another. The fibril mat may,
alternatively, support one binding domain.
[0468] Carbon fibrils may be prepared with chemical functional
groups attached covalently or by physical absorption to their
surface. These and other chemical functional groups can be used to
attach other materials to the surface of fibrils. For example, an
antibody that can be used in an ECL assay can be attached to one or
more fibrils or a fibril mat.
[0469] The fibril mat may be in a single layer containing
underivatized fibrils, derivatized fibrils or a mixture of two or
more different types of fibrils. The fibril mat may have two or
more layers. Successive filtration steps may be used to form mats
of fibrils composed of one or more distinct layers that are either
in contact with or in close proximity to one or more other layers.
For example, a two-layer fibril mat may contain a layer of
underivatized fibrils and a layer of fibrils derivatized with a
biomolecule. In some multi-layered mats, there may be overlap or
mixing between layers.
[0470] The ECL signal that originates from a fibril mat can depend
on the composition of the mat. For example, different
electrochemical potentials may be required to elicit ECL at mats of
derivatized fibrils as compared to mats of underivatized fibrils.
This differences in electrochemical potential can be specific for
or limited to one or more components of an assay. A mat composed of
derivatized fibrils may shift the electrochemical potential at
which the background ECL signal is observed to a different
electrochemical potential than that at which a ECL from a
particular species is observed, i.e., the signal from the
components of the assay that are desirable to measure, and in doing
so, increase resolution between the specific signal and the
background signal.
[0471] Different types of fibrils may be used to prepare fibril
mats with certain capabilities. In mats composed of a layer of
underivatized fibrils and a layer of derivatized fibrils, the layer
of underivatized fibrils may provide an electrical connection
between an electrical conductor and the layer of derivatized
fibrils and also provide physical strength. The layer of
derivatized fibrils contains one or more of the reactants necessary
to conduct an assay. In another embodiment, a mat may contain one
or more fibrils derivatized with a molecule that serves as an
internal standard for calibration of other signals. A mat may also
contain a layer of fibrils that are ECL inactive, the inactive
layer providing physical support for a layer of fibrils that are
ECL active.
[0472] It may be useful to support a fibril mat on another material
e.g. on a porous material such as a filter membrane. The fibril mat
can be formed on the membrane by filtering a suspension of fibrils
through the membrane so as to capture a layer of fibrils on the
surface thereof. Multiple-layer mats can be prepared by successive
filtering of different types of fibrils.
[0473] Electrical connections to fibril mats supported on
non-conducting membranes can be made by contacting one or more
electrically conducting elements, e.g. a wire, a metal mesh or a
metal ring, with a surface of the fibril mat or an electrically
conducting element e.g. an array of metal pins, can be inserted
into or through the fibril mat.
[0474] A filter membrane used to support a fibril mat may be
electrically conducting. Examples of conducting filters include
metal-coated polymer membranes, conducting polymer membranes, metal
meshes, carbon paper, carbon felts, porous metal films, sintered
metal filters, metal-fiber filters and/or metal-fiber papers.
[0475] Metal-coated polymer membranes can be prepared by coating
these with one or more metals by thermal evaporation, electron-beam
evaporation, sputtering, chemical vapor deposition or plating. In a
preferred embodiment, a polymeric filtration membrane is coated
with gold by thermal evaporation.
[0476] Where filter membranes do not capture fibrils efficiently by
filtration, methods can be used to improve filtration efficiency.
The effective pore size of the membrane can be reduced by
deposition of metals on the surface and/or interior regions of the
filter. The filter membrane can be partially plugged or occluded
with a material of appropriate size, i.e. a filter aid can be used.
The filter can be treated chemically to induce binding between the
fibrils and the filter. Binding may be by means of covalent bonds,
van der Waals forces, hydrogen bonding, charge/charge interactions,
or by hydrophobic hydrophilic interactions, or by biospecific
bonding (protein/ligand, antibody/antigen, etc.). The fibrils may
be captured by other mechanisms e.g. deposition on the surface of
the filter by evaporation of the liquid in which they are
suspended.
[0477] A filter that supports a fibril mat can work as an electrode
for ECL. Examples include filters composed of, or coated with,
gold, platinum, carbon, and/or indium-tin oxide(ITO). In such
embodiments, both the support and the fibril mat may contribute to
the observed ECL signal. In some embodiments, a filter that
supports a fibril mat does not function as an electrode for ECL.
Such filters provide support and electrical connectivity for the
fibril mat, but do not contribute to the observed ECL signal
including the background ECL signal.
[0478] Fibril mats can also be supported on non-porous materials.
Fibril mats may be supported on a material capable of acting as an
ECL electrode such as gold foil, platinum foil, conducting
composites or ITO. Fibril mats may be supported on a material that
cannot function as an ECL electrode such as stainless steel, nickel
or non-conducting materials.
[0479] PMAMS can be prepared on fibril mats. The reagents necessary
to form the PMAMs are delivered to spatially distinct regions of a
previously formed fibril mat by microfluidic guides as described
previously. For example, an array of microfluidic guides (G1, G2, .
. . Gn) can be used to deliver biotinylated antibodies (A1, A2 . .
. An) to spatially distinct regions of a mat composed of
streptavidin-coated fibrils. Derivatized fibrils may be delivered
to spatially distinct regions of a support by microfluidic guides
where they are captured, e.g. by filtration or evaporation. For
example, an array of microfluidic guides (G1, G2, . . . Gn) can be
used to deliver fibrils (F1, F1, . . . Fn) covalently linked to
antibodies (A1, A2 . . . An) to spatially distinct regions of a
gold-coated ultrafiltration membrane. In yet another method, a
suspension of fibrils may be filtered through a physical mask, e.g.
a wire mesh, placed in contact with a filter membrane so that
fibrils deposit on the filter wherever the filter is exposed by the
spaces between the wires of the mesh.
[0480] The types of assays that can be conducted using PMAMS
immobilized on fibril mats include those described in section 5.10.
Because the fibril mat is porous, it is possible to conduct assays
by flowing the reagents through the fibril mat and in some cases
the underlying support. Because the size of the pores in a fibril
mat may be small (for example, 10-10000 nm), flowing the reagents
through the mat mixes the reagents efficiently. This reduces the
time required to conduct an immunoassay by improving the rate of
mass transfer to the surface of the binding regions. Assays
conducted by wicking a sample into or through the mat benefit
similarly from increased kinetics. Alternatively, the fibril mat
may be soaked in the sample. The fibril mat can also act as a
filter to remove unwanted materials from biological samples.
[0481] Fibril mat electrodes may be used in assays that do not use
ECL. They may be used as solid-phase binding supports for assays
based on fluorescence, chemiluminescence, or ELISA-type formats.
They may be used as electrodes and/or solid phase supports for
assays based on amperometric or potentiometric electrochemical
detection.
5.19. Methods for Increasing Signal to Background
[0482] It has also now been discovered that two or more signals
originating from electrochemiluminescence species in an
electrochemiluminescence assay can be resolved by conducting the
assay at an electrode having at least two zones which have
different electrochemical potentials at which
electrochemiluminescence occurs. By this method it is possible to
resolve signal from background electrochemiluminescence and thereby
significantly improve the performance of the assay.
[0483] Another method for resolving two or more signals originating
from electrochemiluminescence species in an assay comprises
including in the assay a reagent which selectively modulates the
electrochemiluminescence of one of the electrochemiluminescence
species. For example, a reagent can be included which quenches
electrochemiluminescence from one of the species.
[0484] Another method for resolving two or more signals from
electrochemiluminescence species comprises conducting the assay and
an electrode which includes one zone which is inactive for
generating electrochemiluminescence from one or more of the species
in the assay.
[0485] Background signals can be distinguished from a desired
signal in an assay by conducting the assay at an electrode which
induces electrochemiluminescence for the label and for the
background, respectively, at different electrochemical potentials.
Likewise, the signals from two or more species labeled with the
same electrochemiluminescent compound can be distinguished from one
another at an electrode which induces the electrochemiluminescence
from each of the labels at different potentials. These improved
methods can be carried out on composite electrodes, desirably those
comprised of carbon and best results are obtained by those which
have been modified by chemical or physical treatment to change the
electrochemical potential at which electrochemiluminescence takes
place.
[0486] The invention includes methods for performing an
electrochemiluminescence binding assay for an analyte of interest
which comprises the steps of (a) contacting a sample containing
analyte of interest and a label compound capable of
electrochemiluminescence, with an electrode comprising a
multiplicity of carbon fibrils containing a binding domain
containing a reagent capable of binding a component of the assay,
the carbon fibrils having been modified by chemical or physical
treatment to alter the electrochemical potential at which
electrochemiluminescence of at least one species in the assay
occurs; (b) inducing the label compound at said electrode to
luminesce by imposing a voltage thereupon; and (c) detecting the
emitted luminescence.
[0487] The demands of researchers and clinicians make it imperative
to lower detection limits of assays, to increase the sensitivity of
those assays and to increase the speed at which these assays are
performed.
[0488] A critical parameter in meeting these demands is the
optimization of the signal to background ratio. Here, the signal to
background ratio (S/B) is defined as the ratio of the signal from
components of the sample that are desirable to measure, (e.g. an
analyte) to the signal from components of a sample that are not
desirable to measure (e.g. contaminants). Optimization of the S/B
ratio generally involves maximizing the signal from components that
are desirable to measure and minimizing the background signal.
[0489] Various methods are known in the art for increasing the
signal from labeled species. For example, in U.S. Pat. No.
4,652,333 particles labeled with fluorescent, phosphorescent or
atoms fluorescent labels can be concentrated by microfiltration
before a measurement step is performed.
[0490] Various methods are also known in the art for reducing the
background signal. Wash steps have been used to remove
contaminants, unbound analytes, unbound labeled species, or other
components of the sample.
[0491] It is advantageous to resolve two or more signals such that
detection of one or more signals is optimized.
[0492] FIG. 58 illustrates a method in which the electrochemical
potential of the ECL signal for one or more components is shifted.
In FIG. 58A, the ECL signals for two components (A and B) of a
sample appear at similar electrochemical potentials. As such, they
are difficult to resolve. FIG. 58B shows ECL signals for two
components (A' and B') that appear at different electrochemical
potentials. The potential of the ECL signal for component B' has
shifted to a different potential and the ECL signals for components
A' and B' are readily resolved.
[0493] The selective shift in electrochemical potential that is
illustrated in FIG. 58 can be accomplished by choosing a material
for a working electrode according to the electrochemical potentials
at which ECL is elicited from one or more labels in proximity to
the electrode. Alternatively, a material may be modified by
chemical or mechanical treatment so as to change the
electrochemical potential of the ECL signal for one or more
components of a sample.
[0494] The electrode may have two or more regions with different
electrochemical properties so that one region of the electrode
excites an ECL label at a different electrochemical potential than
another region. The electrode may be a two-layered fibril in which
layer 1 has been derivatized with a binding reagent that binds one
or more analytes from a sample and molecules bearing ECL labels and
layer 2, conversely, has not been derivatized. It does not bind the
analytes but can interact with other components of the sample that
give a background ECL signal. As a consequence of the
derivatization, layer 1 has different electrochemical properties
than layer 2. The ECL signal from labeled molecules bound to layer
1 appears at a higher electrochemical potential than the background
ECL signals that originate from layer 2.
[0495] In another embodiment, a compound that changes the
electrochemical properties, e.g. the electrochemical potential at
which ECL is elicited from a label and/or the intensity of the ECL
signal of one or more components in a sample, can be added to the
sample.
[0496] FIG. 59 shows a schematic of another method for resolving
two or more signals. The intensity of the ECL signal for one or
more components of a sample is reduced relative to the intensity of
the ECL signal for other components of the sample. In FIG. 59A, two
components (A and B) have ECL signals that appear at similar
electrochemical potentials. In FIG. 59B, the value of the intensity
of the ECL signal for component B' has become smaller relative to
the intensity of the ECL signal of component A'.
[0497] The selective change in the intensities of ECL signals
illustrated in FIG. 59 can be accomplished by adding a material
that quenches the ECL signal for one or more components of a
sample. Alternatively, The working electrode may have two or more
regions with different electrochemical properties, e.g., an
electrode may have one or more regions (R1) that can trigger ECL
("ECL-active") and one or more regions (R2) that cannot trigger ECL
("ECL-inactive"). Components (A1) of a sample bound to regions R1
give an ECL signal in the presence of an appropriate
electrochemical potential while the components (B2) of a sample
bound to R2 give no ECL signal.
[0498] The term "ECL-inactive" can also describe regions of an
electrode that produce a non-zero ECL signal that is substantially
smaller than the ECL signal from other regions of an electrode or a
different electrode. A given material may be ECL-active under some
conditions, e.g. in the presence of buffers or certain ECL labels
and be ECL-inactive under different conditions.
[0499] An electrode can be composed of fibrils, which are ECL
active, and a support which is ECL inactive. In this embodiment,
the components of the sample that are in electrochemical contact
with the fibrils emit an ECL signal when the proper electrochemical
potential is applied. In contrast, components of the sample that
are in electrochemical contact with the ECL-inactive support and
not the fibrils do not give an ECL signal when the electrochemical
potential is applied.
[0500] The optical opacity of an electrode can be used to
selectively prevent detection of ECL signals from one or more
components of a sample (see Sec. 5.11 and FIG. 29).
[0501] An electrode may be ECL active for one or more components of
a sample and ECL inactive for other components.
[0502] In another embodiment, one or more components (A.sub.n) of a
sample can be in electrochemical contact with an ECL active
electrode and one or more components (B.sub.n) of a sample can be
out of electrochemical contact with an ECL electrode, i.e. they are
not in sufficient proximity to the electrode. When an appropriate
electrochemical potential is applied to the electrode, an ECL
signal originates from components A.sub.n and not from components
B.sub.n. An electrode may consist of a porous, ECL active layer
bearing one or more binding domains for analytes A.sub.n and a
porous, ECL inactive layer. When a sample is filtered through this
electrode, some analytes A.sub.n bind to the ECL active layer, and
unbound components are captured in the ECL-inactive layer. When a
potential is applied to the electrode, ECL is triggered for the
bound components A, since they are bound to an ECL active layer,
but not for the other components, since they are entrained in an
ECL inactive layer. The invention is further described in the
following examples which are in no way intended to limit the scope
of the invention.
5.20. ECL Assays Employing Sonication
[0503] The disclosure of commonly-owned copending U.S. patent
application Ser. No. 08/932,985 entitled ASSAY SONICATION APPARATUS
AND METHODOLOGY filed on even date herewith is hereby incorporated
by reference in its entirety. In many diagnostic systems wherein
binding reactions occur between reagents, improved mixing of the
reagents can increase the speed of the reaction. Often, the slow
rate of mixing ultimately limits the speed with which a diagnostic
test proceeds to completion. Examples of diagnostic assays wherein
binding reactions between reagents occur include immunoassays,
DNA-probe assays, clinical chemistry tests, receptor-ligand binding
assays, and the like. The slow rate of binding kinetics has been an
especially limiting constraint in conducting assays that
incorporate binding reactions between reagents in solution and
reagents present on a solid. Sonication improves the mixing of
reagents in solution and the mass transport of reagents in solution
to reagents located on or near a surface of a solid. Experiments
have proven that sonication of assay reagents dramatically
decreases the time required to conduct a binding assay that
utilizes a solid-phase support. Sonication is defined to encompass
vibration having a frequency between approximately 100 Hz and 10
MHz. The frequency of sonication (f.sub.s) can be sub-divided into
the following ranges: low-frequency sonication (100
Hz.ltoreq.f.sub.s 5 KHz), ultrasonication (between 5
KHz.ltoreq.f.sub.s 1 MHz), and ultra-high sonication (1
MHz.ltoreq.f.sub.s<10 MHz). The amplitude of the vibrations can
be sub-divided into the following ranges: low amplitude sonication
(<1 .mu.m), medium amplitude sonication (1-10 .mu.m) and high
amplitude sonication (>10.mu.).
[0504] The improved mixing achieved by sonication finds ready and
useful application in both end-point and kinetic assays. In an
end-point assay, the concentration or amount of an analyte of
interest is determined by measuring how much binding has occurred
when the binding reaction has approached completion. We have found
that sonication during the course of the binding reaction decreases
the time required for the binding reaction to approach completion.
In a kinetic assay, the concentration or amount of an analyte of
interest is determined by measuring the rate of the binding
reaction. Similarly, it has been found that sonication during the
course of the binding reaction increases the rate of the binding
reaction. The faster binding reaction produces measurable signals
in much less time than previously possible. The invention so
greatly accelerates the rates of certain reactions that assays
utilizing such reaction may be completed in only a matter of
minutes, often in less than three minutes.
[0505] The rate of a mass transport-limited binding reaction on a
solid support may be a function of both the concentration of the
soluble reagent and the mass-transport coefficient for the
mass-transfer of that reagent to the solid support. Therefore, it
is especially important that the amount, rate, and type of
sonication applied during a kinetic assay be carefully controlled
and be precisely reproducible. Variations in the mass-transfer
coefficients are likely to cause variations in reaction rate among
otherwise identical tests and, consequently, render imprecise or
entirely unusable results. The use of a sonication device
structurally coupled to an assay cell and/or to a solid-phase
support enables the conduct of kinetic binding assays that are
quick, quantitative, highly sensitive, and reproducible.
[0506] It has been found that ECL sandwich immunoassays using
capture antibodies located on a working electrode, the binding
reaction can take more than 1/2 hour to reach completion, even when
vortexing is used to increase mass transport to the solid-support
surface. This time scale is also typical of other highly sensitive
solid-phase binding assays, such as ELISA and RIA. Unexpectedly, we
found that sonication of reagents reduced the time required for
completion of these binding reactions to a matter of minutes. The
apparatus and methodology of the invention is not limited to
immunoassays and will be useful for a wide variety of binding
interactions (e.g., nucleic acid hybridization, antigen-antibody,
receptor-ligand, enzyme-substrate, etc.).
[0507] Sonication is also advantageously employed in systems where
the solid-phase support has a plurality of binding domains, and
each of said binding domains reside on a different location on the
solid phase support. In this case obtaining accurate and
reproducible results requires that the sample be mixed sufficiently
so that all portions of the sample are exposed to all binding
domains. Sonication, by making mass transport efficient, enables
this process.
[0508] It is also advantageously employed in systems where the
solid-phase support has a plurality of binding domains, some or all
of said finding domains being specific for a different analyte.
Obtaining accurate and reproducible results requires that all
portions of the sample be exposed to all binding domains on the
support (e.g. if a certain portion of the sample was not properly
mixed, and therefore was not exposed to a region of the binding
surface that had a binding domain specific for the analyte
contained in said portion of the sample, a false "negative" result
could be obtained.
[0509] Apparatus according to the invention provide a more-than
three-fold increase in the ECL signal produced by a solution
containing TAG1 and the ECL coreactant tripropylamine (TPA) when
the experimental cell is sonicated during the excitation of ECL.
The present invention can, therefore, be applied to the more
sensitive ECL detection of ECL labels and ECL coreactants.
[0510] Sonication will not only increase the rate of mass transport
of reagents to a surface of a solid but will also increase the rate
of mass transport of reagents, products, byproducts, contaminants,
and the like away from the surface. Sonication can be used to
increase the rate of displacement reactions, e.g., the displacement
by an unlabeled analyte present in a sample of a labeled analyte
bound to a binding reagent. Sonication may also be used to increase
the rate of desorption of undesired contaminants on a solid-phase
support, thus, reducing the amount of interference and non-specific
binding produced in a particular assay. Further, sonication may
increase the rate of adsorption of desired materials, such as a
protective coating, or the like, and increase the rate of
desorption of expended or otherwise undesirable materials, such as
a protective coating, or the like. Sonication may be used to
re-suspend particulate contamination, e.g., cell membranes or
particulate reagents, that has settled on a surface.
[0511] Sonication may also be used in a sample preparation step.
For example, sonication may be used to disrupt materials such as
biological tissue cells, microorganisms, virus particles and the
like, to release components of the materials into the reaction
media. Preferably, said sample preparation occurs, in situ, in a
measurement cell, e.g., an ECL cell.
[0512] Still further, sonication may be used to decrease the time
needed to mix two or more solutions to homogeneity, the time needed
to dissolve a solid in a solution, and the time needed to rehydrate
a dried material. Sonication is also useful in increasing the rate
of fluid flow through thin capillaries.
[0513] Sonication may be created by a variety of mechanical and
electromechanical devices. Such devices include electric motors
with an eccentrically mounted cam, electromagnetic speakers,
crystal oscillators, pendulum devices, and the like. A preferred
device for creating sonication at a frequency and amplitude
particularly suitable for the present invention incorporates a
piezoelectric material. Piezoelectric materials are generally
inexpensive, commonly available, lightweight, and can be induced to
sonicate over a wide range of frequencies and amplitudes.
Conveniently, piezoelectric sonication devices are usually rather
small in size, making them especially useful in desktop and
portable devices. Most advantageously, piezoelectric devices may be
operated with very small amounts of electrical power. Sonication
apparatus according to the present invention are effectively
sonicated with piezoelectric devices that consume less than ten
watts, and a particular apparatus functions with a piezoelectric
device consuming approximately 0.25 watts. A preferred
piezoelectric device is a piston-mass device.
[0514] It was further discovered that structural coupling of
sonicating energy from a sonication generator to a cell containing
assay materials is a remarkably efficient design. The most
effective structural coupling has proven to be solid contact, e.g.
by direct attachment of the sonication generator to the cell or
attachment of the sonication generator so that a solid continuum is
provided between the sonication generator and the assay cell. By
specifically transmitting sonication energy to the assay cell or to
a solid-phase support in the assay cell, much less energy is needed
as compared to inducing an entire apparatus to sonicate. Careful
positioning of the sonication generator allows focused direction of
the energy of the contents of the assay cell and lessens the
effects of damping by other elements of an assay system. Structural
coupling may be reversible (e.g. the sonication generator and the
cell may be designed to be connected and unconnected multiple
times) or may represent a permanent connection.
[0515] It is to be understood that structural coupling of
sonication energy can be achieved with many different types of
configurations. The structural coupling of sonication energy
specifically encompasses the transmission of sonication energy (a)
through a solid interface between a sonication generator and an
assay medium or binding surface; or (b) from a sonication generator
directly to an assay medium or to a binding surface.
[0516] It is an important advantage of the invention that the
structural coupling of sonication energy in apparatus according to
the present invention can be precisely controlled. Such control of
the structural coupling mechanism is readily implemented through
precise control of the manufacturing apparatus components and the
assembly of same. Since each component of the structural coupling
mechanism, e.g. the sonication generator, the diaphragm, etc., can
be composed of rigid materials, each component can be manufactured
to precise tolerances. Similarly, the structural coupling mechanism
is suitable for precise, rigid assembly permitting the construction
of multiple apparatuses having virtually identical sonication
transmission characteristics.
[0517] The present invention is generally applicable to binding
assay systems such as immunoassays, nucleic acid hybridization
assays, receptor-ligand binding assays, and the like. In assays
where binding reactions occur in the vicinity of an electrode,
sonication of the electrode itself has proven to have an especially
beneficial effect in increasing assay reaction rates.
[0518] FIG. 68 illustrates a particular cross-sectional view of an
assay cell 68010 according to an embodiment of the present
invention. Assay cell 68010 comprises a base 68011, a diaphragm
68013, and a sonication generator 68016. Base 68011 is shaped to
define a cavity 68017 and an aperture 68014, and is preferably a
rigid material. Alternatively, base 68011 comprises a flexible
material (e.g., base 68011 comprises a flexible plastic container
or a blister pack). In assay formats that use optical detection
techniques (e.g., ECL, fluorescence, chemiluminescence), base 68011
is preferably a transparent material, such as acrylic or the like,
that allows light generated within cavity 68017 to be detected by a
detector (not shown) coupled to base 68011.
[0519] Diaphragm 68013 is a solid-phase support for a reagent
68015, such as a binding reagent, and preferably is comprised of a
thin film or sheet of material. In particular, diaphragm 68013 is
preferably a fibril-polymer composite material. As shown, diaphragm
68013 is coupled to base 68011 at aperture 68014. Preferably,
diaphragm 68013 forms a seal with base 68011 covering aperture
68014.
[0520] Sonication generator 68016 is a device for sonicating
diaphragm 68013. Preferably, sonication generator 68016 comprises a
piezoelectric sonication device. Generator 68016 is preferably
controlled by a sonication generator controller (not shown) such as
an electrical control circuit or the like. Sonication generator
68016 is structurally coupled to diaphragm 68013 so as to
efficiently transmit sonic energy to diaphragm 68013 and to
reagents 68012.
[0521] In operation, reagents 68012 are introduced into cavity
68017. Sonication generator 68016 is energized and sonicates
diaphragm 68013. Diaphragm 68013 conducts the sonication energy to
cavity 68017, and thus to reagents 68012 contained therein. The
sonication causes reagents 68012 to mix, speeding the rate of
reaction among reagents 68012. The sonication will also increase
the rate of mass-transport of reagents, products, byproducts, etc.,
to and from binding reagents 68015 on diaphragm 68013, thus,
speeding the rate of binding reactions at the solid-phase support.
Alternately, binding reagents 68015 may be omitted.
[0522] In an alternate embodiment, a non-solid coupling material
(not shown) is placed between generator 68016 and diaphragm 68013.
The coupling material may be liquid or gas. It is contemplated that
the coupling material may be held in a sealed container, such as a
flexible plastic membrane. In another embodiment, the coupling
material may comprise a solid piston structure. Sonication energy
from sonication generator 68016 is structurally coupled via the
solid piston structure to diaphragm 68013. In a further alternate
embodiment, reagent 68015 is omitted from the surface of diaphragm
and is located on a surface of cavity 68017.
[0523] An assay system 690100 for conducting ECL assays in a
disposable cartridge 69090 with an instrument 690101 is illustrated
in FIG. 69. Cartridge 69090 includes a base 69091, a diaphragm
69092, a counterelectrode 69093, a reaction enclosure 69094, a
sample port 69095, electrical leads 69096, and a reference
electrode 69099. Instrument 690100 includes a cartridge receptacle
690108, a light detector and/or imaging device 690102, an
electrical connector 690103, a source of electrical energy for
applying a voltage or current between the working and counter
electrodes 690104; a sonication device 690105; a source of
electrical energy 690106 for driving sonication device 690105; and
a microprocessor 690107 for instrument control, assay data
gathering, and assay data analysis.
[0524] Diaphragm 69092 is an electrically conductive solid-phase
support for reagents 69097A, such as binding reagents, and
functions as a working electrode. In a preferred embodiment,
diaphragm 69092 is a fibril-polymer composite electrode and
reagents 69097A comprise binding reagents such as antibodies,
nucleic acids, receptors, etc. immobilized thereon. In an
especially preferred embodiment, binding reagents specific for a
variety of analytes are patterned into binding domains on diaphragm
69092. Base 69091 is preferably a rigid and transparent material,
such as acrylic or the like, that allows light generated by an ECL
reaction occurring within enclosure 69094 to be detected by
detector 690102. Base 69091 is shaped to define reaction enclosure
69094 and sample port 69095. Diaphragm 69092 is preferably sealed
to base 69091.
[0525] Electrical leads 69096 are electrical contacts providing
electrical coupling to diaphragm 69092 and to counter electrode
69093. Preferably, diaphragm 69092 is mounted such that the
transmission of sonication energy from device 690105 to base 69091
is minimized. Alternatively, diaphragm 69092 may be mounted so that
diaphragm 69092 transmits sonication energy from device 690105 to
base 69091, and thereon to the entire surface of reaction enclosure
69094.
[0526] Preferably, reaction enclosure 69094 is partially defined by
the inner surface of base 69091. Alternatively, reaction enclosure
69094 may comprise a separate enclosure made of a transparent
material which couples to base 69091.
[0527] Counter electrode 69093 is preferably an electrically
conductive material, such as metal. Reference electrode 69099 is
preferably an Ag/AgCl reference electrode. Electrodes 69093 and
69099 are disposed within base 69091, are coupled to leads 69096,
and are adapted to be in electrical contact with reagents 69098.
Optionally, reference electrode 69098 may be omitted. Aperture
69095 is preferably adapted for insertion of sample material (e.g.,
reagents 69098) via a small tube (not shown), such as a capillary
tube.
[0528] The inner surface of instrument 690101 is adapted to receive
and align cartridge 69090 and its components with receptacle 690108
and its counterpart components, including sonication device 690105,
electrical connections 690103 and detector 690102. Preferably,
detector 690102 is an array of detectors (e.g., a CCD camera or a
photodiode array) that can image the light emitted during an ECL
reaction at the working electrode. Detector 690102 may be a single
detector such as a photomultiplier tube, a photodiode, or the like.
Insertion of cartridge 69090 in instrument 690101 aligns detector
690102 with base 69091 such that detector 690102 is positioned to
detect much of the light produced within enclosure 69094.
[0529] Sonication device 690105 is a device for sonicating
diaphragm 69092 which transmits the sonication energy to reagents
69098 contained in reaction enclosure 69094. Insertion of cartridge
69090 in instrument 690101 preferably aligns device 690105 with the
center of diaphragm 69092 such that device 690105 may be moved into
contact with diaphragm 69092. Insertion of cartridge 69090 in
instrument 690101 causes sonication device 690105 to be
structurally coupled to electrode 69092. It is preferred that
sonication device 690105 comprises a piezoelectric sonication
device that may include a piston. Preferably, sonication device
690105 is movable to achieve contact with diaphragm 69092 when
cartridge 69090 is inserted into instrument 690101.
[0530] Upon insertion of cartridge 69090 into receptacle 690108,
electrical leads 69096 are coupled to electrical connections
690103. The source of electrical energy 690104 may be a
controllable voltage or current source adapted for control by
microprocessor 690107. Alternatively, if cartridge 69090 includes a
reference electrode, source 690104 is preferably a
potentiostat.
[0531] Controlled energy source 690106 is preferably a conventional
controllable electronic circuit driving device for controlling the
operation of sonication device 690105. Operation of source 690106
is controlled by microprocessor 690107. Microprocessor 690107 is a
conventional processor device, such as a software-programmed
microprocessor, a microcontroller, or the like. Microprocessor
690107 controls the operation of detector 690102 and energy sources
690104 and 690106, and receives intensity data from detector 690102
along with voltage and/or current data from source 690104.
Preferably, microprocessor 690107 is additionally capable of
processing the assay data and providing a corresponding output to a
user and/or to another device.
[0532] In operation, a sample comprising reagents 69098 is
introduced via sample inlet port 69095 into reaction enclosure
69094. The reagents required for conducting an ECL assay may
already have been added to the sample. Said reagents include: ECL
coreagents (e.g., tripropylamine), ECL moieties (e.g., Ru(II)(bpy)3
or derivatives, preferably linked to an analyte or the binding
partner of an analyte), blocking agents (e.g., BSA), buffers,
exipients, additives and preservatives. In a preferred embodiment,
the cartridge is prestored with some or all of the reagents
required to conduct an assay, shown as reagents 69097B. In an
especially preferred embodiment, reagents 69097B are stored in a
dry form within reaction enclosure 69094.
[0533] To conduct an assay, cartridge 69090 is placed in instrument
690101, sonication device 690105 is structurally coupled to
diaphragm 69092, and device 690105 activated by source 690106 to
sonicate diaphragm 69092. Sonication energy is then transmitted
through diaphragm 69092 to reagents 69098. Depending upon the
mounting of diaphragm 69092, sonication energy may also be
transmitted to base 69091 which will conduct such energy to
reaction enclosure 69094, and thus to reagents 69098.
[0534] The sonication causes reagents 69098 and reagents 69097B to
mix, speeding the rate of reaction among components reagents 69098
and/or 69097B and the rate of mass transfer of reagents 69098
and/or 69097B to and from diaphragm 69092. Sonication energy from
device 690105 significantly increases the rate of mass transfer of
reagents 69098 and/or 69097B to support 69092, thereby increasing
the rate of binding reactions between reagents 69097A and
components of reagents 69097B and 69098, and decreasing the time
required to make an ECL measurement. Electrical energy is applied
to diaphragm 69092 and to electrodes 69093, by source 690104 via
connector 690103 and leads 690106, to cause an
electrochemiluminescent moiety in reactants 69097A, 69097B and/or
69098 to luminesce. The light produced by the ECL reaction may be
measured (or imaged) while sonication device 690105 operates or
thereafter.
[0535] Microprocessor 690107 controls the operation of sources
690104 and 690106 and receives intensity data from detector 690102
along with voltage and/or current data from source 690104.
Microprocessor 690107 analyzes, and may store, the received data
and preferably produces a corresponding output for provision to a
user or to another device (not shown). Preferably, upon completion
of data collection, microprocessor 690107 notifies the user that
cartridge 69090 may be removed from instrument 690101. Upon
receiving such notification from microprocessor 690107, or
otherwise determining that assay data collection is complete, the
cartridge 69090 is removed from device 690101 and suitably disposed
of or recycled.
[0536] In an alternate embodiment of system 690100, that portion of
leads 69096 coupled to diaphragm 69092 is omitted and an electrical
connection is added between source 690104 and sonication device
690105. Accordingly, the corresponding connection of connector
690103 may also be omitted. In this embodiment, sonication device
690105 functions as the electrical correction to diaphragm 69092.
When cartridge 69090 is inserted into instrument 690101, electrical
energy is provided through sonication device 690105 to reagents
69098 via diaphragm 69092. Such application of electrical energy
may or may not be simultaneous with the application of sonication
energy.
[0537] In an alternate embodiment, diaphragm 69092 and/or enclosure
69094 are pre-coated with a reagent or the like. Sonication of
electrode 69092 may cause such reagent to loosen, allowing the
reagent to mix with reagents 69098 within enclosure 69094.
[0538] In another alternative embodiment, a dry reagent 69097B is
prestored in reaction enclosure 69094 and liquid reagents 69098 are
introduced into reaction enclosure 69094 to directly contact dry
reagent 69097B. Upon activation of sonication device 690105, dry
reagent 69097B and liquid reagent 69098 intermix at a significantly
faster rate than in the absence of sonication energy. The
intermixed reagents may react e.g., with each other and/or with
reagents on a solid-phase support 69092, or another reagent may
then be added and also intermixed. In a different embodiment,
reagent 69097B is omitted.
[0539] The interior surfaces of reaction enclosure 69094 may become
coated with a substance that interferes with an assay. This
interfering substance may include a contaminant, cellular debris, a
non-specifically bound reagent, a reaction byproduct, or the like.
In yet another embodiment of the invention, sonication device
690105 is activated and the sonication energy removes the
interfering substances from the interior surfaces of enclosure
69094 by sonicating such substances to loosen or by causing
increasing the rate of mass transport at the surfaces. For example,
an ECL assay may use cleaning cycles involving activation of device
690105 before and/or after the binding reaction to properly prepare
the electrode for the excitation of ECL. These cleaning cycles may
involve adding to reaction enclosure 69094 a cleaning solution
which assists in loosening such interfering substances.
[0540] In still another alternate embodiment, sonication device
690105 and source 690106 are omitted from instrument 690101 and
diaphragm 69092 additionally comprises a sonication device like
device 690105. Further, source 690104 incorporates the
functionality of source 690106. Electrical power from source 690104
to activate the sonication device of diaphragm 69092 is conducted
via connector 690103 and leads 69096.
[0541] In continuous or intermittent ECL measurements, the rate of
a binding reaction is measured continuously or at intermittent
intervals. A description of this process is found in U.S. Pat. No.
5,527,710 (Nacamulli et al.). The present invention will act to
increase the rate of binding reactions in such assays, and will
also provide reproducible mixing so as to provide precise and
reproducible rate measurements. Sonication may also be continuous
or intermittent during such assays. An advantage of continuous or
intermittent measurements for determining the rate of a binding
reaction is that it offers increased sensitivity and precision as
compared to single-point ECL measurements.
6. EXAMPLES
[0542] All carbon fibrils used in these examples were CC fibrils
obtained from Hyperion Catalysis Incorporated, Lot Number 166-39-1.
These fibrils had diameters that ranged approximately from 3.5 nm
to 70 nm, with lengths greater than 10 times the diameter, an outer
region of multiple layers of carbon atoms and a distinct inner core
region.
6.1. Preparation of an MAB PMAMS Surface by Micro-Stamping
[0543] An exposed and developed photoresist master of 1-2 microns
thickness is prepared according to well known procedures in a
square array pattern. A 10:1 mixture of SYLGARD silicone elastomer
184 (poly(dimethylsiloxane); available from Dow Corning) and the
corresponding SYLGARD 184 curing agent is poured over the master
and cured. The polymerized SYLGARD 184 is carefully removed from
the silicon master. The resulting elastomeric stamp is "inked" by
exposure to a hydrophilic OH-terminated terminated alkane thiol,
SH(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.6OH, in an ethanolic
solution (1-10 mM), robotically brought into pin registered contact
with an aligned gold surface, and removed. The substrate is then
washed for a few seconds (e.g., 2-10 seconds) with a solution of a
hydrophobic CH.sub.3-terminated alkane thiol,
SH(CH.sub.2).sub.10CH.sub.3 (1-10 mM in ethanol) (Kumar et al.,
supra and Prime et al., Science 252:1164-7). The resulting surface
is then gently dried under a stream of nitrogen. A capillary array
containing hydrophilic solutions is then robotically brought into
pin registered contact with the aligned surface aligning the
capillaries with the
SH(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.6OH domains. Each
capillary in the capillary array contains monoclonal antibodies
(MABs), specific for an analyte of interest, capable of covalently
binding to the reactive OH groups on the hydrophilic domains
through an amide linkage.
6.2. Preparation of an MAB and Nucleic Acid PMAMS Surface by
Micro-Stamping
[0544] An exposed and developed photoresist master of 1-2 microns
thickness is prepared according to well known procedures in a
square array pattern. A 10:1 mixture of SYLGARD silicone elastomer
184 and the corresponding SYLGARD 184 curing agent is poured over
the master and cured. The polymerized SYLGARD 184 is carefully
removed from the silicon master. The resulting elastomeric stamp is
"inked" by exposure to a hydrophilic OH-terminated alkane thiol,
SH(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.6OH, in an ethanolic
solution (1-10 mM), robotically brought into pin registered contact
with an aligned gold surface, and removed. The substrate is then
washed for a few seconds (e.g., 2-10 seconds) with a solution of a
hydrophobic CH.sub.3-terminated alkane thiol,
SH(CH.sub.2).sub.10CH.sub.3 (1-10 mM in ethanol) (Kumar et al.,
supra and Prime et al., Science 252:1164-7). The resulting surface
is then gently dried under a stream of nitrogen. A capillary array
containing hydrophilic solutions is then robotically brought into
pin registered contact with the aligned surface aligning the
capillaries with the
SH(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.6OH domains. Each
capillary in the capillary array contains antibodies or modified
nucleic acids, specific for an analyte of interest, capable of
covalently binding to the reactive OH groups on the hydrophilic
domains through amide bond linkages.
6.3. Preparation of a PMAMS Surface by Etching
[0545] A clean gold surface is exposed to a hydrophilic
OH-terminated alkane thiol,
SH(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.6OH (Prime et al.,
Science 252:1164-1167) in an ethanolic solution (1-10 mM). A linear
array of fine tipped etching utensils is robotically brought into
optically registered contact with an aligned gold surface, and the
linear array is used to etch in both the X and Y dimensions of the
surface creating a two dimensional grid array of
SH(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.6OH domains. The
substrate is then washed for a few seconds (eg. 2-10 seconds) with
a solution of a hydrophobic
SH(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.6CH.sub.3 (1-10 mM in
ethanol). The resulting surface is then gently dried under a stream
of nitrogen. A capillary array containing hydrophilic solutions is
then robotically brought into pin registered contact with the
surface aligning the capillaries with the
SH(CH.sub.2).sub.11--(OCH.sub.2 CH.sub.2).sub.6OH domains. Each
capillary in the capillary array contains antibodies or nucleic
acids, specific for an analyte of interest, capable of covalently
binding to the reactive OH groups on the hydrophilic domains.
6.4. Sandwich Assay on a PMAMS Surface
[0546] A transparent PMAMS surface is made as described above which
is substantially transparent with a patterned multi-specific array
of primary antibodies linked to the surface. The support, electrode
assay, monologues surface use selected to be transparent. The PMAMS
surface is then exposed to a solution sample suspected of
containing an analyte of interest to be assayed. The sample is then
washed away leaving antibody bound analytes on the surface. The
PMAMS surface is then exposed to a solution containing secondary
ECL-labeled antibodies specific for bound analytes on the surface.
This solution is then washed from the PMAMS surface leaving ECL
labeled secondary antibodies bound to the domains where analyte is
present.
[0547] The electrode assay is protected by a removable barrier to
prevent premature contact of the sample with the electrode surface
in order to avoid contamination effects. The barrier is then
removed and the electrode array, that is wetted with assay buffer,
is brought into aligned contact with the PMAMS surface. The
electrode array is connected to an electronic potential wave form
generator, and potential is applied to working
electrode/counterelectrode pairs. A CCD then reads the light
emitted and the signal is sent to a microprocessor which converts
the signal to the desired readout form.
[0548] The readout is compared to the readout obtained using
controls in the form of known quantities of an analyte of interest
to calculate the actual quantity of analyte.
6.5. Assay on a First and Second PMAMS Surface
[0549] A transparent PMAMS surface is made as described above with
a patterned multi-specific array of primary antibodies linked to
the surface. The PMAMS surface is then exposed to a solution sample
suspected of containing an analyte of interest to be assayed. The
sample is then washed away leaving antibody bound analytes on the
surface.
[0550] A second PMAMS, under a protective cover, is provided, with
an alternating hydrophobic/hydrophilic pattern on which there are
patterned micro-drops of a plurality of secondary antibodies
labeled with ECL tag.
[0551] The barrier protecting the second PMAMS in register with the
first PMAMS is removed and the micro-drops are brought into
register with the primary antibody binding domains on the first
PMAMS. The second PMAMS is lifted off and the electrode array and
is brought into aligned contact with the first PMAMS surface. The
electrode array is connected to an electrical potential wave form
generator, and potential is applied to working
electrode/counterelectrode pairs. A photo multiplier tube then
reads the light emitted and the signal is sent to a microprocessor
which converts the signal to the desired readout form.
[0552] The readout is compared to the readout obtained using
controls in the form of known quantities of an analyte of interest
to calculate the actual quantity of analyte.
6.6. Nucleic Acid Assay on a PMAMS Surface
[0553] A transparent PMAMS surface is made as described above with
a patterned multi-specific array of single-stranded nucleic acid
probes linked to the surface. The probes are complementary to the
5' region of a nucleic acid analyte of interest. The PMAMS surface
is then exposed to a solution sample suspected of containing a
hybridizable nucleic acid analyte of interest to be assayed, the
sample having been previously denatured, i.e., treated to render
the analyte of interest single stranded. The sample is then washed
away leaving hybridized analytes on the surface. The PMAMS surface
is then exposed to a solution containing secondary ECL labeled
nucleic acid probes specific for the 3' terminus of the nucleic
acid analytes bound on the surface. This solution is then washed
from the PMAMS surface leaving ECL labeled nucleic acid probes
bound to the domains where analyte is present.
[0554] The barrier protecting the second PMAMS in register with the
first PMAMS is removed and the micro-drops are brought into
register with the primary antibody binding domains on the first
PMAMS. The second PMAMS is lifted off and the electrode array and
is brought into aligned contact with the first PMAMS surface.
[0555] The electrode array is connected to an electronic potential
wave form generator, and potential is applied to working
electrode/counterelectrode pairs. A CCD then reads the light
emitted and the signal is sent to a microprocessor which converts
the signal to the desired readout form.
[0556] The readout is compared to the readout obtained using
controls in the form of known quantities of an analyte of interest
to calculate the actual quantity of analyte.
6.7. Competitive Assay on a PMAMS Surface with a Photomultiplier
Detector
[0557] A transparent PMAMS surface is made as described above with
a patterned multi-specific array of primary antibodies, specific
for an analyte of interest, linked to the surface. The PMAMS
surface is then exposed to a solution sample to be assayed which is
a mixture of a sample suspected of containing the analyte of
interest and a known amount of an ECL labeled molecule competitive
with the analyte of interest for binding to the antibodies. The
sample is then washed away leaving antibody bound analytes and/or
labelled competitive binders on the surface.
[0558] The electrode array is protected by a removable barrier to
prevent contact of the sample with the electrode surface in order
to avoid contamination effects. The barrier is then removed and the
electrode array, that is wetted with assay buffer, is brought into
aligned contact with the PMAMS surface. The electrode array is
connected to a electronic potential wave form generator, and
potential is applied to working electrode/counterelectrode pairs. A
photomultiplier tube then reads the light emitted and the signal is
sent to a microprocessor which converts the signal to the desired
readout form.
[0559] The readout is compared to the readout obtained using
controls in the form of known quantities of an analyte of interest
to calculate the actual quantity of analyte.
6.8. Competitive Assay on a PMAMS Surface with a CCD Detector
[0560] A transparent PMAMS surface is made as described above with
a patterned multi-specific array of primary antibodies linked to
the surface. The PMAMS surface is then exposed to a solution sample
suspected of containing the analyte of interest to be assayed. The
sample is then washed away leaving antibody bound analytes on the
surface.
[0561] A second PMAMS, under a protective cover, is provided with
an alternating hydrophobic/hydrophilic pattern on which there are
patterned micro-drops of a plurality of a known amount of an ECL
labeled molecule competitive with an analyte of interest.
[0562] The barrier protecting the second PMAMS in register with the
first PMAMS is removed and the micro-drops are brought into
register with the primary antibody binding domains on the first
PMAMS. The second PMAMS is lifted off and the electrode array is
brought into aligned contact with the PMAMS surface. The electrode
array is connected to a electronic potential wave form generator,
and potential is applied to working electrode/counterelectrode
pairs. A CCD then reads the light emitted and the signal is sent to
a microprocessor which converts the signal to the desired readout
form.
[0563] The readout is compared to the readout obtained using
controls in the form of known quantities of an analyte of interest
to calculate the actual quantity of analyte.
6.9. Preparation of an MAB PMAMS Surface by Micro Stamping with an
SH(CH.sub.2).sub.10CH.sub.3 Alkane Thiol
[0564] An exposed and developed photoresist master of 1-2 microns
thickness is prepared according to well known procedures in a
square array pattern. A 10:1 mixture of SYLGARD silicone elastomer
184 (poly(dimethylsiloxane); available from Dow Corning) and the
corresponding SYLGARD 184 curing agent is poured over the master
and cured. The polymerized SYLGARD 184 is carefully removed from
the silicon master. The resulting elastomeric stamp is "inked" by
exposure to a hydrophilic OH-terminated alkane thiol,
SH(CH2).sub.11OH, in an ethanolic solution (1-10 mM), robotically
brought into pin registered contact with an aligned gold surface,
and removed. The substrate is then washed for a few seconds (e.g.,
2-10 seconds) with a solution of a hydrophobic CH.sub.3-terminated
alkane thiol, SH(CH.sub.2).sub.10CH.sub.3 (1-10 mM in ethanol)
(Kumar et al., supra). The resulting surface is then gently dried
under a stream of nitrogen. A capillary array containing
hydrophilic solutions is then robotically brought into pin
registered contact with the aligned surface aligning the
capillaries with the SH(CH.sub.2).sub.11OH domains to place
specific antibodies at each domain. Each capillary in the capillary
array contains monoclonal antibodies, specific for an analyte of
interest, capable of covalently binding to the reactive OH groups
on the hydrophilic domains.
6.10. Preparation of an MAB And Nucleic Acid PMAMS Surface by
Micro-Stamping with an SH(CH.sub.2).sub.10CH.sub.3 Alkane Thiol
[0565] An exposed and developed photoresist master of 1-2 microns
thickness is prepared according to well known procedures in a
square array pattern. A 10:1 mixture of SYLGARD silicone elastomer
184 and the corresponding SYLGARD 184 curing agent is poured over
the master and cured. The polymerized SYLGARD 184 is carefully
removed from the silicon master. The resulting elastomeric stamp is
"inked" by exposure to a hydrophilic OH-terminated alkane thiol,
SH(CH.sub.2).sub.11OH, in an ethanolic solution (1-10 mM),
robotically brought into pin registered contact with an aligned
gold surface, and removed. The substrate is then washed for a few
seconds (e.g., 2-10 seconds) with a solution of a hydrophobic
CH.sub.3-terminated alkane thiol, SH(CH.sub.2).sub.10CH.sub.3 (1-10
Mm in ethanol) (Kumar et al., supra). The resulting surface is then
gently dried under a stream of nitrogen. A capillary array
containing hydrophilic solutions is then robotically brought into
pin registered contact with the aligned surface aligning the
capillaries with the SH(CH.sub.2).sub.11OH, domains to place
specific antibodies and/or hybridizable nucleic acids at each
domain. Each capillary in the capillary array contains antibodies
or modified nucleic acids, specific for an analyte of interest,
capable of covalently binding to the reactive OH groups on the
hydrophilic domains through amide bond linkages.
6.11. Preparation of a PMAMS Surface Using a Streptavidin-Biotin
Linker
[0566] An exposed and developed photoresist master of 1-2 mm
thickness is prepared according to well known procedures in a
square array pattern. A 10:1 mixture of SYLGARD silicone elastomer
184 and the corresponding SYLGARD 184 curing agent is poured over
the master and cured. The polymerized SYLGARD 184 is carefully
removed from the silicon master. The resulting elastomeric stamp is
"inked" by exposure to a mixture of mercaptoundecanol and
12-mercapto(8-biotinamide-3,6-dioxaoctyl)dodecanamide where the
mole fraction of the biotinylated thiol is 0.1 (see Spinke et al.,
1993, Langmuir 9:1821-5 and Spinke et al., 1993, J. Chem. Phys.
99(9): 7012-9). The substrate is then washed for a few seconds
(e.g., 2-10 seconds) with a solution of a hydrophobic
CH.sub.3-terminated alkane thiol, HS(CH.sub.2).sub.10CH.sub.3
alkane thiol (1-10 mM in ethanol) (see Kumar et al. supra,
Biebuyck, Whitesides). The resulting surface is then gently dried
under a stream of nitrogen. A capillary array containing a solution
of streptavidin in each capillary is then robotically brought into
pin registered contact with the aligned surface. Each capillary in
the capillary array is aligned and brought into contact with a
biotinylated domain and the capillary array is removed and the
surface washed. A second capillary array containing a multiplicity
of biotinylated antibodies and biotinylated nucleic acids solutions
is then robotically brought into pin registered contact with the
aligned surface to place specific antibodies and nucleic acids on
each domain.
6.12. Preparation of an MAB Single Surface
[0567] An electrode array of interdigitating working and
counterelectrode pairs on a gold on silicon surface is fabricated
through methods known in the art (for example see Kumar et al
supra). In this example, the electrode array and the discrete
binding domain array exist on the same surface of a support. An
exposed and developed photoresist master of 1-2 microns thickness
is prepared according to well known procedures in the pattern of
the working electrodes. A 10:1 mixture of SYLGARD silicone
elastomer 184 (poly(dimethylsiloxane(PDMS)); available from Dow
Corning) and the corresponding SYLGARD 184 curing agent is poured
over the master and cured. The polymerized SYLGARD 184 is carefully
removed from the silicon master. The resulting elastomeric stamp is
"inked" by exposure to a hydrophilic OH-terminated alkane thiol,
SH(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.6OH, in an ethanolic
solution (1-10 mM), robotically brought into pin registered contact
with the aligned working electrodes on gold electrode array
surface, and is then removed. A capillary array containing
hydrophilic solutions is then robotically brought into pin
registered contact by aligning the capillaries with the
SH(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.6OH domains on the
electrode array surface to place specific antibodies on each
domain. Each capillary in the capillary array contains monoclonal
antibodies, specific for an analyte of interest, capable of
covalently binding to the reactive OH groups on the hydrophilic
domains through an amide linkage.
6.13. Assay Conducted on an MAB Single Surface
[0568] A support as described 6.12, supra, is fabricated. A PDMS
stamp is fabricated as previously described from a photoresist
master patterned as rings which each independently circumscribe a
working electrode/counterelectrode pair. The electrode array
surface is then exposed to a sample to be analyzed, washed with a
mixture of ECL labelled secondary antibodies, and then washed with
an assay buffer solution containing tripropyl amine. The PDMS stamp
is then aligned and brought into registered contact aligning the
rings of the PDMS stamp so as to circumscribe and define individual
volume elements of assay buffer above each electrode pair. An
overpotential is applied to the electrode pairs so as to release
the monolayer from the surface exposing the working electrode to
the ECL labelled secondary antibodies. A photomultiplier tube then
reads the light emitted through the transparent PDMS and the signal
is sent to a microprocessor which converts the signal to the
desired readout form.
[0569] The readout is compared to the readout obtained using
controls in the form of known quantities of an analyte of interest
to calculate the actual quantity of analyte.
6.14. Preparation of a Single Surface with Working and
Counterelectrodes
[0570] An electrode array of interdigitating working and counter
gold electrode pairs with gold binding domains in between the
interdigitating electrodes on a gold on silicon support is
fabricated through methods known in the art (for example see Kumar
et al. supra). In this example, the electrode array and the
discrete binding domain array exist on the same surface. An exposed
and developed photoresist master of 1-2 microns thickness is
prepared according to well known procedures in the pattern of the
binding domains in between the interdigitating electrode pairs. A
10:1 mixture of SYLGARD silicone elastomer 184
(poly(dimethylsiloxane(PDMS)); available from Dow Corning) and the
corresponding SYLGARD 184 curing agent is poured over the master
and cured. The polymerized SYLGARD 184 is carefully removed from
the silicon master. The resulting elastomeric stamp is "inked" by
exposure to a hydrophilic OH-terminated alkane thiol,
SH(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.6OH, in an ethanolic
solution (1-10 mM), robotically brought into pin registered contact
with the aligned gold binding domains on the electrode array
surface, and is then removed. A capillary array containing
hydrophilic solutions is then robotically brought into pin
registered contact, aligning the capillaries with the
SH(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.6OH domains on the
electrode array surface to place specific antibodies on each
domain. Each capillary in the capillary array contains antibodies
specific for an analyte of interest, capable of covalently binding
to the reactive OH groups on the hydrophilic domains through an
amide linkage.
6.15. Assay Conducted on a Single Surface with Working and
Counterelectrodes
[0571] A support surface as described 6.14 supra is fabricated by
the described methods. The prepared surface is exposed to a sample
to be analyzed, washed with a mixture of ECL labelled secondary
antibodies, and then washed with an assay buffer solution
containing tripropyl amine. The electrode array is connected to a
electronic potential wave form generator, and potential is applied
to working electrode/counterelectrode pairs. A photomultiplier tube
then reads the light emitted and the signal is sent to a
microprocessor which converts the signal to the desired readout
form.
[0572] The readout is compared to the readout obtained using
controls in the form of known quantities of an analyte of interest
to calculate the actual quantity of analyte.
6.16. Preparation of a Surface with Counterelectrodes
[0573] An exposed and developed photoresist master of 1-2 microns
thickness is prepared according to well known procedures in a
square array pattern. A 10:1 mixture of SYLGARD silicone elastomer
184 and the corresponding SYLGARD 184 curing agent is poured over
the master and cured. The polymerized SYLGARD 184 is carefully
removed from the silicon master. The resulting elastomeric stamp is
"inked" by exposure to a hydrophilic OH-terminated alkane thiol,
SH(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.6OH, in an ethanolic
solution (1-10 mM), robotically brought into pin registered contact
with an aligned patterned counterelectrode and square binding
domain on a gold surface, and removed. The patterned gold surface
consists of addressable ring counterelectrodes circumscribing the
binding domains where the
SH(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.6OH has been stamped.
A gap or separation space exists between each gold counterelectrode
and each square gold substrate for each monolayer binding domain. A
capillary array containing binding reagent solutions is then
robotically brought into pin registered contact with the aligned
surface registering the capillaries with the
SH(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.6OH domains to place
specific antibodies or nucleic acids on each domain. Each capillary
in the capillary array contains antibodies or nucleic acids,
specific for an analyte of interest, capable of covalently binding
to the reactive OH groups on the hydrophilic domains.
6.17. Assay Conducted on a Single Surface with the Working and
Counterelectrodes on Different Surfaces
[0574] The support surface described above in example 6.16 is
exposed to a sample solution to be analyzed. The support surface is
then washed and exposed to a solution containing a plurality of ECL
labelled monoclonal antibodies or ECL labelled nucleic acids of
differing specificity and then washed with assay buffer containing
tripropyl amine. A transparent addressable working electrode array
is fabricated with each working electrode in the array
corresponding to a discrete binding domain/counterelectrode region
on the support as described above in Section 6.16. The two supports
are wetted with the assay buffer and robotically brought into
registered aligned conformal contact. The electrode arrays are
connected to an electronic potential wave form generator, and
potential is applied to the aligned working
electrode/counterelectrode pairs creating a potential field between
the two supports. A CCD then reads the light emitted through the
transparent working electrode and the signal is sent to a
microprocessor which converts the signal to the desired readout
form.
[0575] The readout is compared to the readout obtained using
controls in the form of known quantities of an analyte of interest
to calculate the actual quantity of analyte.
6.18. Fabrication of a CC (Dispersed) Fibril MAT by Vacuum
Filtration
[0576] An aqueous slurry of CC fibrils, with 1 mg fibrils/mL
solution was prepared by mixing 0.1% w/w CC fibrils/deionized
water. The CC fibrils were dispersed (the larger, micron-scale
aggregates were dispersed into small aggregates or individual
fibers) in the slurry by immersing a 400 watt sonication horn in
the slurry for between 10 minutes and 1 hour. The extent of
dispersion was monitored by optical microscopy.
[0577] A nylon filter membrane (0.47 .mu.m pore size, 25 mm
diameter) was placed in a 25 mm diameter glass fritted filter. The
dispersed fibril slurry was filtered through the membrane/filter
set-up by suction filtration (FIG. 23A). Aliquots of the slurry (5
ml) were diluted with 20 ml deionized water, then filtered through
the membrane/filter set-up. For an average mat of approximately
0.25-0.3 gram/cc, a mat of approximately 100 .mu.m required 6
aliquots.
[0578] Suction filtration was continued until all of the water from
the dispersion was removed from the mat (by visual inspection). The
mat was peeled (by hand) directly from the filter membrane.
[0579] The mat was dried in an oven for approximately 10-15 minutes
at 60.degree. C. The mat was cut, punched or otherwise sectioned
for use.
6.19. Fabrication of a Fibril Mat on a Metal Mesh Support by
Evaporation
[0580] An aqueous slurry of CC fibrils, with 1 mg fibrils/mL
solution was prepared by mixing 0.1% w/w CC fibrils/deionized
water. The CC fibrils were dispersed (the larger, micron-scale
aggregates were dispersed into small aggregates or individual
fibers) in the slurry by immersing a 400 watt sonication horn in
the slurry for between 10 minutes and 1 hour. The extent of
dispersion was monitored by optical microscopy.
[0581] A 1 cm.sup.2 section of stainless steel mesh (400 count) was
placed on a 25 mm diameter paper filter. A 5 ml aliquot of the
slurry was pipetted onto the surface of the screen/filter paper
ensemble. The water in the slurry was allowed to evaporate, either
at room temperature and pressure, or in a heated oven.
[0582] Once the fibril mat was dry, additional aliquots were added.
The fibril and screen were peeled as a single unit from the filter
paper.
[0583] The mat was cut, punched or otherwise sectioned for use.
6.20. Immobilization of Avidin on Fibrils Bearing NHS-Ester
Functional Groups
[0584] Fibrils derivatized with COOH (provided by Hyperion
Catalysts Inc.) were suspended in anhydrous dioxane at .about.10
mg/ml with constant stirring. A 20-fold molar excess of
N-hydroxysuccinimide was added and allowed to dissolve. Next, a
20-fold molar excess of ethyl-diamino-propyl-carbodiimide (EDAC)
was added, and the mixture was stirred for 2 hours at room
temperature.
[0585] After stirring, the supernatant was aspirated and the solids
were washed three times with anhydrous dioxane, one time with
anhydrous methanol, and filtered on a 0.45 .mu.m polysulfone
membrane. The filtrate was washed with additional methanol and the
placed in a glass vial under vacuum until no further reduction in
weight was observed.
[0586] 10.4 mg of NHS-ester fibrils were washed with PBS-1
(.about.70 mM phosphate, 150 mM NaCl) (ORIGEN reagent 402-130-01,
pH 7.8, IGEN, Inc.). The washed fibrils were suspended in 2.3 ml
solution of avidin (8.3 mg avidin/ml PBS-1).
[0587] The suspension was allowed to sit at room temperature for
1.5 hours, with constant rotation of the flask to provide
agitation.
[0588] After 1.5 hours, the suspension was stored for 16 hours at
4.degree. C., then brought to room temperature and washed with
PBS-1 and stored at 4.degree. C. as a suspension in PBS-1.
6.21. Immobilization of Monoclonal Antibody (Anti-AFP) on Carbon
Fibrils
[0589] Carbon fibrils functionalized with NHS esters were prepared
as described in Example 6.20.
[0590] 14 mg of fibril-NHS ester was mixed with 500 ml PBS-1
buffer. The mixture was sonicated for 20 min, until it became a
viscous slurry. An additional 500 ml of PBS-1 buffer was added.
[0591] A total of 1.6 mg anti-AFP (alpha-fetal protein) antibody in
80 ml PBS-1 was added to the above slurry. The reaction was allowed
to sit at room temperature for 2.5 hours.
[0592] 6 ml PBS-1 buffer was added and the reaction mixture was
centrifuged at 4.degree. C. for 5 minutes. The supernatant was
removed by pipette. This procedure was repeated 9 times.
[0593] After the final wash, the supernatant was removed, and the
fibril-antiAFP product was stored at 4.degree. C.
6.22. Cyclic Voltammograms of Fibril Mats: Comparison of Fibril Mat
with Gold Foil Electrode
[0594] Cyclic voltammograms of 6 mM Fe.sup.3+/2+ (CN).sub.6 in 0.5
M K.sub.2SO.sub.4 were measured. In FIG. 30A, the CV for a plain
fibril mat of CC(dispersed) was measured at 0.10 mA/cm at 10, 25
and 50 mV/sec. The mat was fabricated as described in Example 6.18.
In FIG. 30B, the CV was measured for a gold foil electrode at 0.05
mA/cm at 10, 25 and 50 mV/sec. All potentials are in Volts vs.
Ag/AgCl.
6.23. Electrochemical Properties of Fibril Mat Electrodes:
Comparison of Anodic Peak Current with Thickness of the Mat
[0595] Cyclic voltammograms of 6 mM Fe.sup.3+/2+ (CN).sub.6 in 0.5
M K.sub.2SO.sub.4 were measured for fibril mats of the same
geometric area (0.20 cm.sup.2), but different thicknesses. The
anodic peak current (FIG. 31) increased with increasing thickness
of mat for thicknesses that ranged from 24 .mu.m to 425 .mu.m. For
each thickness, the anodic peak current also increased with
increasing scan rates (for rates that ranged from 10 mV/sec to 150
mV/sec). The rate of increase of the anodic peak current, as a
function of thickness, also increased with increasing thickness.
Fibril mats that were 24 .mu.m thick behaved comparably to gold
foil electrodes.
6.24. Non-Specific Binding of Proteins to Fibrils
[0596] Non-specific binding of proteins to carbon fibrils (cc) was
measured as follows: i) a solution of Ru(bipy).sub.3.sup.2+
("TAG1") labeled proteins was exposed to a known quantity of carbon
fibrils until equilibrium was reached; ii) the
labeled-protein/fibril solution was centrifuged, and the
supernatant was collected, and iii) the amount of labeled-protein
remaining in the supernatant was assayed using
electrochemiluminescence (ECL).
[0597] To generate the curve shown in FIG. 32, anti-CEA antibody
attached to derivatized TAG1 (antibody to carcinoembryonic antigen
attached to a derivatized TAG1 ECL label) at 3 .mu.g/mL, was added
to serial dilutions of CC(plain) fibrils in 0.1 M potassium
phosphate buffer at pH 7. Fibrils were removed by centrifugation
after vortexing for 20 minutes. ECL assays that measured the amount
of protein (unbound) remaining in the supernatant were run in an
ORIGEN 1.5 (IGEN, Inc.) analyzer on aliquots of the reaction
mixture supernatant diluted 5 times with ORIGEN assay buffer. A
decrease in the ECL lative to the ECL signal for an object of the
reaction at had not been exposed to fibrils) resulted from binding
of protein labelled with a derivatized TAG1 her concentration of
carbon fibrils were present.
6.25. Reduction of Non-Specific Binding of Proteins to Fibrils with
Detergents/Surfactants
[0598] Using the method described in Example 6.2.4, the effect of
surfactant on protein binding to fibrils was analyzed. Triton X-100
added to the anti-CEA attached to derivatized TAG1/fibril mixture,
the solution was incubated for 20 minutes, the tubes were
centrifuged, and aliquots of the supernatant, diluted 5 times with
ORIGEN assay buffer, were analyzed by ECL. The results are shown in
the Table below and in FIG. 33.
TABLE-US-00001 Tube [T-X100], Peak Prot-TAG1 [GF], Number ppm
Intensity .mu.g/ml ppm 19 1674 1611 2.65 52 18 837 1634 2.65 52 17
418 1697 2.65 52 16 209 1583 2.65 52 15 105 1772 2.65 52 14 52 1463
2.65 52 13 26 627 2.65 52 12 13 23 2.65 52
A curve that results from plotting the ECL intensity of a protein
labelled with a derivatized TAG1 in solution vs. Triton X-100
concentration is shown in FIG. 33. A higher ECL signal corresponds
to more derivatized-TAG1-labeled protein in the supernatant, which
corresponds to less derivatized-TAG1-labeled protein bound to the
fibrils. Concentrations of Triton x-100 that ranged from 10 ppm to
100 ppm reduced the extent of binding; increasing the concentration
from 100 to 2000 ppm did not further reduce the extent of
binding.
6.26. ECL of Free Tag in Solution with Fibril Mat Electrode
[0599] A fibril mat prepared as in Example 6.18 was installed in
the mounting area 3403 of the working electrode holder 3401 of the
"Fibril Cell" fixture shown in FIG. 34. The holder 3401 was slipped
into the bottom of the electrochemical cell compartment 3400. The 3
M Ag/AgCl reference electrode (Cyprus # EE008) was installed into
the electrochemical cell compartment through the reference cell
hole 3402. The cell was filled with Assay Buffer (IGEN # 402-005-01
lot# 5298) and attached to the PMT holder 3404. Using a EG&G
PARC model 175 universal programmer and an EG&G model 175
Potentiostat/Galvanostat the potential was swept from 0 V to +3 V
vs. Ag/AgCl at 100 mV/s. The ECL was measured by a Hamamatsu
R5600U-01 which was powered at 900V by a Pacific Instruments model
126 Photometer. The analog data was digitized at 10 Hz by a
CIO-DAS-1601 A/D board driven by HEM Snap-Master. The Fibril Cell
was drained, flushed with 1000 pM TAG1 (IGEN # 402-004-C lot#
4297), and filled with 1000 pM TAG1. The potential was swept as
with Assay Buffer. Shown in FIG. 35 are the ECL traces (measured at
24.0.+-.0.2 C) for Assay Buffer 3501 and 1000 pM TAG1 3502. The
dark corrected ECL peak area was 22.10 nAs for Assay Buffer and
46.40 nAs for 1000 pM TAG1.
6.27. ECL of Adsorbed Labeled Antibody with Fibril Mat
Electrode
[0600] Fibril mats were made to a thickness of 0.0035 inches from
plain cc-dispersed fibrils in the manner described in Example 6.18.
The dried mats were then punched into 3 mm disks and mounted onto
supports. The supports used in this experiment were fabricated from
0.030 inches polyester sheet patterned by screen printed conductive
gold ink. This conductive gold ink formed the counter electrode,
reference electrode, and provided leads for the working and other
electrodes. Two fibril mat disks were mounted to each patterned
support using two sided carbon containing conductive tape
(Adhesives Research). After mounting, the disks were spotted with
0.5 .mu.l of 10 .mu.g/ml anti-TSH antibody attached to derivatized
TAG1 in deionized water (Ru-TSH mono 1:2 26JUN95, IGEN, Inc.) or
0.5 .mu.l of 10 .mu.g/ml anti-TSH unTAG1' ed capture antibody in
deionized water (TSH poly 25JUN95, IGEN, Inc.) and allowed to dry.
After drying, the mats were flooded with IGEN assay buffer. Flooded
mats on supports were loaded into an IGEN Origen 1.5 based
instrument and ECL was read using a scan rate of 500 mV/s from 0 to
4500 mV. FIG. 43 compares the peak ECL signals from TAG1-antibody
containing mats 4301 and unTAG1' ed capture antibody containing
mats 4302.
6.28. ECL Using Fibril Mat Electrode for Sandwich Assay
[0601] Anti-AFP capture antibody was immobilized on fibrils as
described above. Anti-AFP fibrils were washed into deionized water
(dI) and resuspended at a density of 1 mg/ml. A four layer fibril
mat was produced using vacuum filtration as described in Example
6.18. Two milligrams of anti-AFP fibrils were added to 3 mg of
plain CC dispersed fibrils and the mixture diluted to a total
volume of 20 ml in dI. The diluted mixture was filtered onto a 0.45
.mu.m nylon filter. This initial mat layer was then followed by two
core layers, each consisting of 5 mg of plain CC dispersed fibrils.
The mat core was then topped with a mixed fibril layer identical to
the initial layer. This resulted in a fibril mat that was
.about.40% anti-AFP fibrils on the top and bottom surface and
.about.100% plain fibrils in the core. This mixed mat was air dried
under vacuum and punched into 3 mm disks. These disks were then
mounted onto supports as described in Example 6.27. Dry, supported,
anti-AFP mats were flooded with AFP calibrators A, C, and F (IGEN,
Inc.) and allowed to incubate for 15 minutes at room temperature on
the bench top. After incubation, supported electrodes were washed
with a dI stream for 10 seconds and then blotted dry with a lint
free wipe. Fibril mats were then flooded with anti-AFP attached to
antibody labelled with derivatized TAG1 (IGEN, Inc.) and allowed to
incubate for 15 minutes at room temperature on the bench top. After
incubation the supported electrodes were washed with dI and dried
with a wipe. Fibril mats were then flooded with IGEN assay buffer
and read as described in Example 6.27.
6.29. ECL Detection of TAG1-Labeled Avidin on a Polyacrylamide
Surface
[0602] A cross-linked polyacrylamide gel containing covalently
bound biotin was prepared by copolymerization of acrylamide,
bis-acrylamide, and
N-Acryloyl-N'-biotinyl-3,6-dioxaoctane-1,9-diamine (biotin linked
to an acrylamide moiety through a tri(ethylene glycol) linker)
using well known conditions (initiation with ammonium persulfate
and TEMED). In this experiment, the concentrations of the three
monomeric species were 2.6 M, 0.065 M, and 0.023 M respectively
(these concentrations of acrylamide and bis-acrylamide are reported
to result in gels with pore sizes smaller than most proteins).
Polymerization of the solution containing the monomers between two
glass plates held apart to a distance of approximately 0.7 mm led
to the formation of a slab gel with the same thickness. After the
polymerization reaction was complete, any unincorporated biotin was
washed out by soaking the gel in four changes of PBS. Avidin
labeled with a derivatized TAG1 (where Avidin refers to
NeutrAvidin, a modified avidin designed to exhibit reduced NSB, was
used in this experiment) was bound to the surface of the gel by
soaking the gel in a solution containing the protein at a
concentration of 50 .mu.g/mL in PBS for 20 min. Excess TAG1-labeled
avidin was then washed away by soaking the gel in four changes of
ECL assay buffer (200 mM sodium phosphate, 100 mM tripropylamine,
0.02% (w/v) Tween-20, pH 7.2). As shown in FIG. 39, the gel (3900)
was then placed in contact with gold working (3901) and counter
(3902) electrodes patterned on a glass support (3903). Ramping the
potential across the two electrodes from 0.0 to 3.0 V and back to
0.0 V at a rate of 500 mV/s led to an ECL light signal as measured
from a PMT (3904) placed above the gel (FIG. 40). A gel prepared
without inclusion of the biotin containing acrylamide derivative
gave no ECL signal (FIG. 41). This signal obtained for the
biotin-containing polymer was indicative of close to a full
monolayer of protein is present on the surface of the gel.
6.30. ECL Sandwich Immunoassay on a Polyacrylamide Surface
[0603] A cross-linked polyacrylamide gel containing covalently
bound biotin is prepared as described in Example 6.29. Streptavidin
is adsorbed on the surface of the gel to form a binding domain
capable of capturing biotin labeled species. The surface is treated
with a solution containing tripropylamine, an unknown concentration
of an analyte, a biotin-labeled antibody against the analyte, and a
different ECL TAG1-labeled antibody against the analyte. The
presence of the analyte causes the formation of a complex of the
analyte and the two antibodies which is then captured on the
streptavidin surface. ECL tag bound to secondary antibody present
on the surface is measured as described in example 6.29
6.31. Multiple ECL Sandwich Immunoassays on Polyacrylamide Surfaces
Supported on an Electrode
[0604] An exposed and developed photoresist master of 1-2 microns
thickness is prepared according to well known procedures to give a
pattern of circular depressions arranged in an array. A 10:1
mixture of SYLGARD silicone elastomer 184 and the corresponding
SYLGARD 184 curing agent is poured over the master and cured. The
polymerized SYLGARD is carefully removed from the silicon master.
The resulting elastomeric stamp is "inked" by exposure to a
solution containing the hydroxyl terminated thiol
HS--(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.3--OH (1-10 mM) in
ethanol, brought into contact with an aligned gold substrate and
removed. The substrate is washed for several seconds with a
solution containing the thiol HS--(CH.sub.2).sub.10--CH.sub.3 (1-10
mM in ethanol). The resulting surface is then rinsed with ethanol
and dried under a stream of nitrogen. Treatment of the surface with
a solution containing acryloyl chloride and triethylamine in
dioxane leads to functionalization of the hydroxyl terminated
domains with acrylate groups. A capillary array containing mixtures
of acrylamide, bis-acrylamide, N-acryloylsuccinimide,
azo-bis-cyanovaleric acid, and antibodies presenting amino groups
is then brought into contact with the aligned surface aligning the
capillaries with the acrylate terminated domains to place
prepolymer solutions containing specific antibodies at each domain.
Each capillary in the capillary array contains antibodies specific
for a different analyte of interest. Exposure of the patterned
prepolymer droplets to UV light leads to the formation of
cross-linked gels on the substrate each presenting a binding domain
at the surface. The assay is carried out by treatment of the
substrate with a mixture of analytes capable of binding at one or
more of the binding domains presented on the gel surfaces in a
buffered solution containing tripropylamine and ECL-TAG1 labeled
secondary antibodies. The binding domains (4200, 4201, 4202) (on
polyacrylamide drops (4203) on a gold electrode (4232) are then
placed in close proximity to an ITO working electrode (4204) as
shown in FIGS. 42A-B. Light emitted from each of the binding
domains is quantified using a CCD camera (4205) and compared to
binding domains for internal standards included in the sample
solution.
6.32. Multiple ECL Competitive Immunoassays on Polyacrylamide
Surfaces Supported on an Electrode
[0605] An exposed and developed photoresist master of 1-2 microns
thickness is prepared according to well known procedures to give a
pattern of circular depression arranged in an array. A 10:1 mixture
of SYLGARD silicone elastomer 184 and the corresponding SYLGARD 184
curing agent is poured over the master and cured. The polymerized
SYLGARD is carefully removed from the silicon master. The resulting
elastomeric stamp is "inked" by exposure to a solution containing
the hydroxyl terminated thiol
HS--(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.3--OH (1-10 mM) in
ethanol, brought into contact with an aligned gold substrate and
removed. The substrate is washed for several seconds with a
solution containing the thiol HS--(CH.sub.2).sub.10--CH.sub.3 (1-10
mM in ethanol). The resulting surface is then rinsed with ethanol
and dried under a stream of nitrogen. Treatment of the surface with
a solution containing acryloyl chloride and triethylamine in
dioxane leads to functionalization of the hydroxyl terminated
domains with acrylate groups. A capillary array containing mixtures
of acrylamide, bis-acrylamide, N-acryloylsuccinimide,
azo-bis-cyanovaleric acid, and antibodies is then brought into
contact with the aligned surface aligning the capillaries with the
acrylate terminated domains to place prepolymer solutions
containing specific antibodies at each domain. Capillaries in the
capillary array contain antibodies specific for different analytes
of interest. Exposure of the patterned prepolymer droplets to UV
light leads to the formation of cross-linked gels on the substrate
each presenting a binding domain at the surface. The assay is
carried out by treatment of the substrate with a mixture of
analytes capable of binding at one or more of the binding domains
presented on the gel surfaces in a buffered solution containing
tripropylamine and ECL-TAG1 labeled analogues of the analytes
(i.e., setting up a competition of ECL-TAG1 labeled and unlabeled
analytes for binding to the binding domains). The binding domains
(4200, 4201 and 4202) (on polyacrylamide drops (4203) on a gold
electrode (4232)) are then placed in close proximity to an ITO
working electrode (4204) as shown in FIG. 42. Light emitted from
each of the binding domains is quantified using a CCD camera (4205)
and compared to binding domains for internal standards included in
the sample solution.
6.33. Multiple ECL Assays for Binding of Cells on Polyacrylamide
Surfaces Supported on an Electrode
[0606] An exposed and developed photoresist master of 1-2 microns
thickness is prepared according to well known procedures to give a
pattern of circular depressions arranged in an array. A 10:1
mixture of SYLGARD silicone elastomer 184 and the corresponding
SYLGARD 184 curing agent is poured over the master and cured. The
polymerized SYLGARD is carefully removed from the silicon master.
The resulting elastomeric stamp is "inked" by exposure to a
solution containing the hydroxyl terminated thiol
HS--(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.3--OH (1-10 mM) in
ethanol, brought into contact with an aligned gold substrate and
removed. The substrate is washed for several seconds with a
solution containing the thiol HS--(CH.sub.2).sub.10--CH.sub.3 (1-10
mM in ethanol). The resulting surface is then rinsed with ethanol
and dried under a stream of nitrogen. Treatment of the surface with
a solution containing acryloyl chloride and triethylamine in
dioxane leads to functionalization of the hydroxyl terminated
domains with acrylate groups. A capillary array containing mixtures
of acrylamide, bis-acrylamide, N-acryloylsuccinimide,
azo-bis-cyanovaleric acid, and antibodies directed against cell
surfaces is then brought into contact with the aligned surface
aligning the capillaries with the acrylate terminated domains to
place prepolymer solutions at each domain. Exposure of the
patterned prepolymer droplets to UV light leads to the formation of
cross-linked gels on the substrate each presenting a binding domain
at the surface. The assay is carried out by treatment of the
binding domains first with a suspension of cells, then with a
mixture of binding reagents capable of binding one or more of the
cells bound to the gel surfaces in a buffered solution containing
tripropylamine and ECL-TAG1 labeled secondary antibodies and/or
other binding reagents specific for the analytes. The binding
domains (4200, 4201, and 4202) (on polyacrylamide drops (4203) on a
gold electrode (4232) are then placed in close proximity to an ITO
working electrode (4204) as shown in FIG. 42. Light emitted from
each of the binding domains is quantified using a CCD camera (4205)
and compared to binding domains for internal standards included in
the sample solution.
6.34. Multiple ECL Assays for Binding of Analytes to Cells on
Polyacrylamide Surfaces Supported on an Electrode
[0607] An exposed and developed photoresist master of 1-2 microns
thickness is prepared according to well known procedures to give a
pattern of circular depressions arranged in an array. A 10:1
mixture of SYLGARD silicone elastomer 184 and the corresponding
SYLGARD 184 curing agent is poured over the master and cured. The
polymerized SYLGARD is carefully removed from the silicon master.
The resulting elastomeric stamp is "inked" by exposure to a
solution containing the hydroxyl terminated thiol
HS--(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.3--OH (1-10 mM) in
ethanol, brought into contact with an aligned gold substrate and
removed. The substrate is washed for several seconds with a
solution containing the thiol HS--(CH.sub.2).sub.10--CH.sub.3 (1-10
mM in ethanol). The resulting surface is then rinsed with ethanol
and dried under a stream of nitrogen. Treatment of the surface with
a solution containing acryloyl chloride and triethylamine in
dioxane leads to functionalization of the hydroxyl terminated
domains with acrylate groups. A capillary array containing mixtures
of acrylamide, bis-acrylamide, N-acryloylsuccinimide,
azo-bis-cyanovaleric acid, and cells is then brought into contact
with the aligned surface aligning the capillaries with the acrylate
terminated domains to place prepolymer solutions containing
specific cell types at each domain. Capillaries in the capillary
array contain cells with different surface structures that bind
different analytes. Exposure of the patterned prepolymer droplets
to UV light leads to the formation of cross-linked gels on the
substrate each presenting a binding domain at the surface. The
assay is carried out by treatment of the gels with a sample
containing a mixture of analytes capable of binding at one or more
of the binding domains presented on the gel surfaces in a buffered
solution containing tripropylamine and ECL-TAG labeled antibodies
and/or other binding reagents specific for the analytes. The
binding domains (4200, 4201 and 4202) (on polyacrylamide drops
(4203) on a gold electrode (4232) are then placed in close
proximity to an ITO working electrode (4204) as shown in FIG. 42.
Light emitted from each of the binding domains is quantified using
a CCD camera (4205) and compared to binding domains for internal
standards included in the sample solution.
6.35. Multiple ECL Competitive Hybridization Assays on
Polyacrylamide Surfaces Supported on an Electrode
[0608] An exposed and developed photoresist master of 1-2 microns
thickness is prepared according to well known procedures to give a
pattern of circular depression arranged in an array. A 10:1 mixture
of SYLGARD silicone elastomer 184 and the corresponding SYLGARD 184
curing agent is poured over the master and cured. The polymerized
SYLGARD is carefully removed from the silicon master. The resulting
elastomeric stamp is "inked" by exposure to a solution containing
the hydroxyl terminated thiol
HS--(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.3--OH (1-10 mM) in
ethanol, brought into contact with an aligned gold substrate and
removed. The substrate is washed for several seconds with a
solution containing the thiol HS--(CH.sub.2).sub.10--CH.sub.3 (1-10
mM in ethanol). The resulting surface is then rinsed with ethanol
and dried under a stream of nitrogen. Treatment of the surface with
a solution containing acryloyl chloride and triethylamine in
dioxane leads to functionalization of the hydroxyl terminated
domains with acrylate groups. A capillary array containing mixtures
of acrylamide, bis-acrylamide, N-acryloylsuccinimide,
azo-bis-cyanovaleric acid, and nucleic acid probes functionalized
with amino groups is then brought into contact with the aligned
surface, aligning the capillaries with the acrylate terminated
domains to place prepolymer solutions containing specific probes at
each domain. Capillaries in the capillary array contain probes
specific for a nucleic acid sequence of interest. Exposure of the
patterned prepolymer droplets to UV light leads to the formation of
cross-linked gels on the substrate, each presenting a binding
domain at the surface. The assay is carried out by treatment of the
substrate with a sample mixture that may contain sequences capable
of binding at one or more of the binding domains presented on the
gel surfaces in a buffered solution containing tripropylamine and
ECL-TAG1 labeled sequences which can compete with the analytes of
interest for binding to the surface. The binding domains (4200,
4201, and 4202) (on polyacrylamide drops (4203) on a gold electrode
(4232) are then placed in close proximity to an ITO working
electrode (4204) as shown in FIG. 42. Light emitted from each of
the binding domains is quantified using a CCD camera (4205) and
compared to binding domains for internal standards included in the
sample solution.
6.36. Multiple ECL Hybridization Sandwich Assays on Polyacrylamide
Surfaces Supported on an Electrode
[0609] An exposed and developed photoresist master of 1-2 microns
thickness is prepared according to well known procedures to give a
pattern of circular depression arranged in an array. A 10:1 mixture
of SYLGARD silicone elastomer 184 and the corresponding SYLGARD 184
curing agent is poured over the master and cured. The polymerized
SYLGARD is carefully removed from the silicon master. The resulting
elastomeric stamp is "inked" by exposure to a solution containing
the hydroxyl-terminated thiol
HS--(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.3--OH (1-10 mM) in
ethanol, brought into contact with an aligned gold substrate and
removed. The substrate is washed for several seconds with a
solution containing the thiol HS--(CH.sub.2).sub.10--CH.sub.3 (1-10
mM in ethanol). The resulting surface is then rinsed with ethanol
and dried under a stream of nitrogen. Treatment of the surface with
a solution containing acryloyl chloride and triethylamine in
dioxane leads to functionalization of the hydroxyl terminated
domains with acrylate groups. A capillary array containing mixtures
of acrylamide, bis-acrylamide, N-acryloylsuccinimide,
azo-bis-cyanovaleric acid, and nucleic acid probes functionalized
with amino groups is then brought into contact with the aligned
surface, aligning the capillaries with the acrylate terminated
domains to place prepolymer solutions containing specific probes at
each domain. Capillaries in the capillary array contain probes
specific for a nucleic acid sequence of interest. Exposure of the
patterned prepolymer droplets to UV light leads to the formation of
cross-linked gels on the substrate, each presenting a binding
domain at the surface. The assay is carried out by treatment of the
substrate with a sample mixture that may contain sequences capable
of binding at one or more of the binding domains presented on the
gel surfaces in a buffered solution containing tripropylamine and
ECL-TAG1 labeled sequences which can bind the analytes at sequences
not complementary to the surface-bound probes. The binding domains
(4200, 4201, and 4202) (on polyacrylamide drops (4203) on a gold
electrode (4232) are then placed in close proximity to an ITO
working electrode (4204) as shown in FIG. 42. Light emitted from
each of the binding domains is quantified using a CCD camera (4205)
and compared to binding domains for internal standards included in
the sample solution.
6.37. Multiple Assays of Different Types on a Polyacrylamide
Surfaces Supported on an Electrode
[0610] An exposed and developed photoresist master of 1-2 microns
thickness is prepared according to well known procedures to give a
pattern of circular depressions arranged in an array. A 10:1
mixture of SYLGARD silicone elastomer 184 and the corresponding
SYLGARD 184 curing agent is poured over the master and cured. The
polymerized SYLGARD is carefully removed from the silicon master.
The resulting elastomeric stamp is "inked" by exposure to a
solution containing the hydroxyl terminated thiol
HS--(CH.sub.2).sub.11--(OCH.sub.2CH.sub.2).sub.3--OH (1-10 mM) in
ethanol, brought into contact with an aligned gold substrate and
removed. The substrate is washed for several seconds with a
solution containing the thiol HS--(CH.sub.2).sub.10--CH.sub.3 (1-10
mM in ethanol). The resulting surface is then rinsed with ethanol
and dried under a stream of nitrogen. Treatment of the surface with
a solution containing acryloyl chloride and triethylamine in
dioxane leads to functionalization of the hydroxyl terminated
domains with acrylate groups. A capillary array containing mixtures
of acrylamide, bis-acrylamide, N-acryloylsuccinimide,
azo-bis-cyanovaleric acid, and any of the binding reagents
described in Examples 6.31-6.36 is then brought into contact with
the aligned surface aligning the capillaries with the acrylate
terminated domains to place prepolymer solutions containing
specific probes at each domain. Each capillary in the capillary
array contains binding domains specific for analytes of interest.
Exposure of the patterned prepolymer droplets to UV light leads to
the formation of cross-linked gels on the substrate each presenting
a binding domain at the surface. The assay is carried out by
treatment of the substrate with a sample mixture that may contain
analytes capable of binding at one or more of the binding domains
presented on the gel surfaces in a buffered solution containing
tripropylamine and either ECL-TAG1 labeled analogues of analytes
which compete with analytes for binding to the binding domains
and/or ECL-TAG1 labeled secondary binding reagents to the analytes
of interest. The binding domains (4200, 4201, and 4202) (on
polyacrylamide drops (4203) on a gold electrode (4232) are then
placed in close proximity to an ITO working electrode (4204) as
shown in FIG. 42. Light emitted from each of the binding domains is
quantified using a CCD camera (4205) and compared to binding
domains for internal standards included in the sample solution.
6.38. Highly Reversible ECL
[0611] Polycrystalline gold electrodes (purchased from
Bio-Analytical Services, 2 mm.sup.2) were cleaned by hand polishing
sequentially with 0.5 .mu.m and 0.03 .mu.m alumina slurry, followed
by chemical etching in 1:3 H.sub.2O.sub.2/H.sub.2SO.sub.4 and
electrochemical cycling in dilute H.sub.2SO.sub.4 between -0.2 V
and 1.7 V vs. Ag/AgCl. The clean electrodes were then immersed
overnight in a dilute solution of octylthiol (C.sub.8SH) dissolved
in ethanol. Protein adsorption was carried out by covering
C.sub.8SH-modified electrodes with 20 .mu.l of TAG1-labeled bovine
serum albumin (BSA) dissolved in phosphate buffer saline (PBS, 0.15
M NaCl/0.1 M NaPi, pH 7.2) and washing the surface extensively with
the same buffer after ten minute incubation.
[0612] ECL was done in a three-electrode cell with a Ag/AgCl
reference electrode, platinum wire counter electrode and an
EG&G 283 potentiostat. The light intensity was measured with a
Pacific Instruments photometer and a Hamamatsu photo-multiplier
tube placing at the bottom of the electrochemistry cell. The
protein-adsorbed electrode was immersed in a solution of 0.1 M TPA
and 0.2 M phosphate, pH 7.2. Highly reversible ECL response
(substantially similar intensity on the forward and backward scans)
was observed when the electrode potential was cycled between 0.0 V
and 1.2 V, as shown in FIG. 44A, indicating the reversible nature
of the ECL process and stability of the thiol and protein layers on
the electrode.
[0613] Cyclic voltammetric experiments were conducted on the same
instruments as for ECL, without the use of PMT and photometer. In
the experiment, a C.sub.8SH-covered electrode (no protein) was
placed in a solution of 1 mM potassium ferricyanide (in PBS) and
the electrode was scanned from +0.5 V to 1.2 V and back, followed
by another cycle between +0.5 V and -0.3 V. It is indicative that
the monolayer is still intact and not desorbing at 1.2 V, since
there was only capacitive current in the voltammogram between +0.5
V and -0.3 V and no faradaic current of ferricyanide (FIG.
44B).
6.39. Quasi-Reversible ECL
[0614] Electrode modification and protein adsorption were done in
the same way as described above. In the ECL experiments, the
potential was scanned between 0.0 V and 1.5 V, and the
corresponding light intensity was recorded. As illustrated in FIG.
45A, there was some loss of ECL between the forward and backward
scans of the same cycle, as well as between different cycles.
Cyclic voltammograms of the thiol/Au in ferricyanide after
oxidizing at 1.5 V showed a significant amount of faradaic current,
indicative of at least partial desorption of the thiol monolayer at
1.5 V (FIG. 45B).
6.40. Irreversible ECL
[0615] In these experiments, electrode modification and protein
adsorption were conducted in the same way as in Example 6.38. To
measure ECL, the electrode potential was scanned all the way up to
2.0 V and back to 0.0 V. Intense light was observed on the forward
scan (more light than was observed under reversible conditions in
Example 6.38), but it dropped to the background on the reverse
scan, as shown in FIG. 46A. Cyclic voltammograms of the modified
electrode in ferricyanide after oxidizing at 2.0 V indicated most
of the thiol monolayer was desorbed (FIG. 46B).
6.41. An ECL Sandwich Immunoassay Using a Primary Antibody
Immobilized on a Patterned Gold Electrode
[0616] In this example an antibody against prostrate specific
antigen (PSA) is immobilized on a patterned gold electrode for use
in an immunoassay for PSA.
[0617] An exposed and developed photoresist master of one to two
microns thickness is prepared according to well known procedures to
give a layer of photoresist on a silicon support with a 1
mm.times.1 mm square patch where photoresist is removed. A 10:1
mixture of SYLGARD silicone elastomer 184 and the corresponding
curing agent is poured over the master and cured. The polymerized
SYLGARD is carefully removed from the silicon master. The resulting
elastomeric "stamp" is "inked" by exposing it to a solution
containing the hydroxyl-terminated thiol
HS--(CH.sub.2).sub.11(OCH.sub.2CH.sub.2).sub.3--OH and the
nitrilotriacetic acid (NTA) terminated-thiol
HS--(CH.sub.2).sub.11(OCH.sub.2CH.sub.2).sub.3OC(O)NH(CH.sub.2).sub.4CH(C-
O.sub.2H)N(CH.sub.2CO.sub.2H).sub.2 in ethanol. The "inked" stamp
is brought into contact with a gold substrate and removed to form a
1 mm.times.1 mm SAM. The substrate is washed for several seconds
with a solution containing only the hydroxl-terminated thiol in
ethanol, to prevent non-specific binding of proteins to the regions
outside the stamped feature. The resulting surface is then rinsed
with ethanol and dried under a stream of nitrogen. Treatment of the
surface with a solution of NiCl.sub.2 followed by treatment with a
solution containing a fusion protein presenting the binding sites
of an anti-PSA mouse monoclonal and the peptide (His).sub.6, leads
to immobilization of the fusion protein on the surface in a
controlled manner. This process yields a reproducible and
predetermined amount of immobilized protein on the surface. The
orientation of the protein on the surface is controlled by the
location of the (His).sub.6 sequence in the primary structure of
the fusion protein. The absolute amount of immobilized protein is
controlled by the ratio of NEA terminated-thiol to
hydroxy-terminated thiol in the stamped SAM and by the surface area
of the stamped feature. A calibration curve for PSA is determined
by preparing solutions containing known concentrations of PSA in
serum (at concentrations ranging from 1 fM to 1 uM. A number of
surfaces prepared as described above are treated with the PSA
calibration standards and then with a solution containing a
secondary antibody against PSA (labeled with a derivative of TAG1)
at an optimized concentration. A calibration curve is determined by
immersing the surfaces in a solution containing 0.1 M TPA and 0.2 M
phosphate (pH 7.2), and measuring the peak intensity of light
emitted when the electrical potential at the gold surface is cycled
between 0.0 and 2.0 V at a scan rate of 0.5V/sec. The determination
of unknown concentrations of PSA in serum in a sample is conducted
by the same procedure except that the concentration of PSA is
calculated from the peak ECL signal by reference to the calibration
curve.
6.42. Preparation of Aerosil-200 Silica Particles Coated with
Streptavidin
[0618] Aerosil-200 (Degussa Corporation, Akron, Ohio, USA), a fumed
silica with a particle size of 12 nm and an active surface area of
175-220 m.sup.2/g, was chemically modified to introduce NHS ester
groups. The modification involved three steps: i) amino groups were
introduced to the surface of the particles by reaction with
3-aminopropyltrimethoxysilane. The Aerosil-200 (155.5 mg) was
combined with 3-aminopropyltrimethoxysilane (513 mg) in 5 mL of
toluene and refluxed for 1 hour. The silica particles were washed
two times with 4 mL of toluene, three times with 4 mL of methanol
and three times with 4 mL of dichloromethane. Each wash consisted
of centrifugation of the suspension followed by resuspension of the
pellet in fresh solvent; ii) the amino groups were reacted with
succinic anhydride to introduce carboxylic acid groups to the
surface. The 55.2 mg of washed particles were resuspended in 3 mL
of anhydrous DMF. Succinic anhydride (102 mg) and triethylamine
(0.025 mL) were added and the suspension stirred for 16 h.
Additional succinic anhydride (50 mg) was added and the reaction
was allowed to proceed for another 3 hours. Excess reagent was
removed by washing the particles two times with DMF, once with
methanol, and two times with dichloromethane; and iii) the
carboxylic acid groups on the surface were activated as
N-hydroxysuccinimide (NHS) esters by reaction with NHS and
ethyl-3-diaminopropylcarbodiimide (EDC). The particles (25.1 mg
were resuspended in 3 mL of methylene chloride. NHS (64 mg) and EDC
(110 mg) were added and the suspension was then stirred for 3
hours. The particles were then washed three times with
dichloromethane and dried under vacuum.
[0619] The activated silica particles were coated with streptavidin
by the reaction of the protein with the NHS esters on the surface
of the activated particles. The particles (.about.1.5 mg) were
added to solution containing 0.750 mg of streptavidin in phosphate
buffered saline (PBS), pH 7.85. The reaction was allowed to proceed
for 16 hours. The particles were then washed with PBS and water and
resuspended in PBS to give a stock suspension containing particles
at a concentration of 0.1 mg/mL.
6.43. Formation of a Fibril Mat on a Support of Stainless Steel
Filter Paper or Use in Particle-Based ECL Assays
[0620] A fibril ink was formed by the sonication of a suspension of
CC fibrils (0.1 mg/mL in 0.2% triton X-100 in water) for 15 minutes
using a probe sonicator (Branson Ultrasonic Corp., Danbury, Conn.,
USA). The suspension was filtered using gentle suction onto an
1/8'' diameter circular region on a disc of stainless steel filter
paper (GA-4, Baekart Fibre Technologies). The thickness of mats
formed by this method was approximately 1 .mu.m/mL of added fibril
ink.
6.44. A Particle-Based ECL Assay For AFP Using Streptavidin-Coated
Beads Captured on a Fibril Mat
[0621] An AFP assay was run using the following steps: i) formation
of a sandwich immune complex on the surface of beads in suspension;
ii) filtration of the beads onto a fibril mat supported on
stainless steel filter paper; and iii) detection of ECL from
TAG1-labeled antibodies in the immune complexes by scanning the
fibril electrode to an oxidizing potential. The assay was run using
an AFP assay kit (Boehringer-Mannheim). This assay kit is designed
for ECL-based assays using the Elecsys System
(Boehringer-Mannheim); a system which captures magnetic beads on a
platinum electrode by the application of a magnetic field. The
assay kit included the following stock solutions: a suspension
containing streptavidin-coated magnetic beads (M-280, Dynal Inc.),
a biotin-labeled capture antibody (R-1), a TAG1-labeled secondary
antibody (R-2), and a series of calibrators containing AFP
dissolved in a matrix designed to simulate serum.
[0622] To determine a calibration curve for the assay, the stock
suspension of streptavidin-coated beads (0.017 mL containing
.about.0.012 mg of beads) was combined in a plastic tube with the
stock solutions containing R-1 (0.017 mL), R-2 (0.017 mL), and an
AFP calibrator (0.010 mL). The tube was vortexed and then gently
shaken for 30 minutes at room temperature. The suspension was then
filtered using gentle suction onto a fibril mat (mat
thickness=0.030 mm) formed as described in Example 6.43. The mat
was washed with ECL Assay Buffer (IGEN, Inc.). The ECL was then
measured as described in Example 6.26. Each calibrator was run in
triplicate. FIG. 48 shows the background corrected ECL signal as a
function of the concentration of AFP.
6.45. A Particle-Based ECL Assay for APP Using Streptavidin-Coated
Silica Beads Captured on a Fibril Mat
[0623] An AFP assay was run as described in Example 6.44 except
that streptavidin-coated silica particles (Aerosil-200, prepared as
described in Example 6.42) were used instead of the magnetic beads
supplied with the AFP assay kit. To determine a calibration curve
for the assay, the stock suspension of streptavidin-coated
Aerosil-200 (0.010 mL containing 0.001 mg of particles) was
combined in a plastic tube with the stock solutions containing R-1
(0.017 mL), R-2 (0.017 mL), and an AFP calibrator (0.010 mL). The
tube was vortexed and then gently shaken for 30 minutes at room
temperature. The suspension was then filtered using gentle suction
onto a fibril mat (mat thickness=40 mm) formed as described in
Example 6.43. The mat was washed with ECL Assay Buffer (IGEN,
Inc.). The ECL was then measured as described in Example 6.26. Each
calibrator was run in triplicate. FIG. 49 shows the background
corrected ECL signal as a function of the concentration of AFP.
6.46. ECL Emitted from Fluorescent Dye-Labeled Latex Beads Captured
on a Fibril Mat Electrode
[0624] This example describes an experiment showing that
fluorescent dyes incorporated into beads could be used as internal
standards in bead-based ECL assays. Three types of fluorescent
beads were purchased from Polysciences Inc. The beads differed in
the excitation and emission wavelengths of the incorporated dyes:
i) Catalog # 17685 (l.sub.ex=273 nm, l.sub.ex=340 nm). ii) Catalog
# 19392 (l.sub.ex=530 nm, l=590 nm). iii) Catalog # 17797
(l.sub.ex=641 nm, l.sub.em=740 nm). Fibril mats were prepared as
described in Example 6.43. The fluorescent beads (0.010 mg) were
filtered on to the mats using gentle suction. The mats were washed
with ECL Assay Buffer (IGEN, Inc.) and the ECL measured as
described in Example 6.26. Each bead was tested in triplicate. All
three beads emitted ECL under these conditions. The average
integrated ECL signals measured for Polyscience catalog # 17685,
19392, and 17797 beads were 0.7 nAs, 6.0 nAs, and 2.3 nAs,
respectively.
6.47. An ECL Sandwich Immunoassay for AFP Using Biotin-Streptavidin
Capture to Immobilize a Capture Antibody on a Gold Electrode
[0625] In this example, an antibody against alpha-fetoprotein (AFP)
is immobilized on a gold electrode for use in an immunoassay.
[0626] Glass slides (1 cm.times.1 cm.times.0.06 cm) were coated on
one side with a thin gold film by thermal evaporation. The gold
film was formed by the evaporation of 3 nm of Ti as an adhesion
layer followed by 100 nm of Au (99.99%). A self-assembled monolayer
(SAM) was formed on the gold films by incubation of the slides in
an ethanolic solution containing mercaptoundecanoic acid at a
concentration of 1 mM for a period of approximately 10 hours. The
carboxylic acid groups presented at the surface of the SAM were
activated by treatment for 10 minutes with 0.05 mL of an aqueous
solution containing 1-ethyl-3-(3-dimethylaminopropyl)carbodiimide
(EDC) and N-hydroxysuccinimide (NHS) at concentrations of 0.2 M and
50 mM respectively. The surface was then washed briefly with water.
Streptavidin was immobilized on the activated surface by treatment
of the surface for 60 minutes with 0.05 mL of a solution containing
streptavidin at a concentration of 0.3 mg/mL in phosphate buffered
saline (PBS). The surface was blocked by adding 0.08 mL of an
aqueous solution containing 1 M ethanolamine, pH 8.5. After
incubating for 30 minutes the chip was washed with HBS/p20 (10 mM
HEPES, 0.15 M NaCl, 0.005% Tween 20, pH 7.4).
[0627] The AFP assay kit (Boehringer-Mannheim) consists of a stock
solution of biotin labeled primary antibody (0.007 mg/mL), a stock
solution of TAG1-labeled secondary antibody (0.012 mg/mL), and five
calibrator solutions in an artificial matrix designed to simulate
human serum. The assay conditions were not optimized for these
reagents. To conduct an AFP assay, 0.020 ml of the primary antibody
stock, 0.020 ml of the secondary antibody stock, and 0.020 ml of a
calibrator solution were combined and applied to a slide that had
been coated with streptavidin. The solution was incubated on the
surface for 20 minutes. The surface was then washed with HBS/p20
(10 mM HEPES, 0.15 M NaCl, 0.005% Tween 20, pH 7.4).
[0628] ECL was measured on the surface of a slide by the following
procedure: The slide was placed in an electrochemical cell. The
cell contained an O-ring which defined the area of the gold surface
which was electrochemically excited (0.13 cm.sup.2). The cell also
contained a Pt counter electrode and a Ag/AgCl reference electrode
as well as a means to make electrical contact to the gold film. The
cell was held in a defined position under a photomultiplier tube
(PMT) to allow for reproducible detection of ECL emission. To
excite ECL, the electrodes were immersed in assay buffer (0.1 M
tripropylamine, 0.2 M sodium phosphate, 0.02% (w/v) Tween-20, pH
7.2) and the electrical potential at the gold surface ramped from 0
V to 2 V (vs. Ag/AgCl) at a rate of 0.2 V/s. The photocurrent
generated at the PMT was integrated over the duration of the scan
to give an ECL signal in units of nAs.
[0629] FIG. 51 shows a plot of the ECL signal vs. the concentration
of AFP in solution.
6.48. The Detection of Nucleic Acid Hybridization to a Probe
Immobilized on a Gold Electrode
[0630] The oligonucleotides used in this example are defined as
follows:
TABLE-US-00002 SC1.2: 5' ca gtt gtg tgc cac cta caa 3' C6 Disulfide
modifier SC2.3: 5' ttg tag gtg gca cac aac tg 3' C3 Amino Modifier
SC4.1: 5' TAG1-gaa-aat-gtg-ctg-acc-gga-cat-gaa- aat-gag 3'
[0631] The oligonucleotides were purchased from Oligos Etc. Inc.
SC2.3 was labeled with the TAG1 by reaction with a derivative of
TAG1 presenting an NHS ester (NHS-TAG, IGEN Inc.). SC2.3 (130
nmole) in 0.100 ml of PBS pH 7.4 was combined with 0.400 ml of DMSO
in a 0.5 mg vial of TAG-NHS-ester. The solution was mixed and
incubated overnight in the dark at room temperature. Following the
overnight incubation the labeling reaction was diluted with 1.380
ml of deionized water. An aqueous solution containing sodium
chloride at a concentration of 5 M (0.120 mL) was added followed by
0.120 mL of absolute ethanol. This solution was then incubated at
-70.degree. C. for at least 1 hour to precipitate the product. The
labeled oligonucleotide was centrifuged at 5000.times.g for 10
minutes at 10.degree. C. The resulting pellet was washed twice with
0.5 mL of a 70% (v/v) solution of ethanol in water. The washed
pellet was dried under vacuum and stored in the dark at -20.degree.
C. The manufacturer of the SC4.1 oligonucleotide labeled the probe
with TAG1 during the oligonucleotide synthesis by reaction with a
phosphoramidite derivative of TAG1 (IGEN, Inc.).
[0632] Glass slides (1 cm.times.1 cm.times.0.06 cm) were coated on
one side with a thin gold film by thermal evaporation. The gold
films were formed by the evaporation of 4 nm of Ti as an adhesion
layer followed by 200 nm of Au (99.99%). Wells were formed above
the gold films by sealing the slides, with O-rings, against holes
drilled through a block of plastic. The O-rings defined the area of
the gold films in contact with solution (0.25 cm.sup.2). The
oligonucleotide SC1.2 was immobilized on the surface of the gold
films by adding 0.050 mL of a solution containing 0.010 mg of the
oligonucleotide (in 10 mM ammonium acetate, pH 6.0) to each well.
The immobilization was allowed to proceed overnight in a dark
desiccator, during which time the solution containing the
oligonucleotide evaporated to dryness. Excess reagents were then
removed by several washes with deionized water.
[0633] Prehybridization of the oligonucleotides on the surface of
the gold slide was accomplished by the addition of 0.050 mL of a
solution containing the components of SSC solution (1.times.), the
components of Denhardts Solution(1.times.), yeast tRNA (0.100
mg/mL), and sonicated herring sperm DNA (0.050 mg/mL). The slides
were then shaken vigorously for 30 minutes at room temperature.
Following the prehybridization step, the slides were washed with
SSC and hybridized with calibration solutions containing
(1=10.sup.12) molecules of TAG1-labeled SC2.3 (an oligonucleotide
complementary to the sequence immobilized on the surface), or
TAG1-labeled SC4.1 (a non-complementary probe used as a negative
control to test for non-specific binding). The TAG1-labeled probes
were applied as solutions in 0.050 ml of the solution used for
prehybridization. The hybridization was allowed to proceed for 2
hours at room temperature with vigorous shaking. The gold slides
were then washed three times with 1.times.SSC containing 0.1% (w/v)
SDS, incubated with the same buffer for 30 minutes at room
temperature and rinsed with ECL assay buffer (IGEN, Inc.). ECL was
excited from the surface of the gold film as described in Example
6.47. ECL was also excited from a surface that was not exposed to a
TAG1-labeled probe in order to measure the magnitude of the
background signal. The value of the background corrected signal
from the complementary probe was 3.3.times.10.sup.3 nAs, showing
that the TAG1-labeled probe hybridized to the surface and could be
detected by ECL. The value of the background corrected signal from
the non-complementary probe was -2.2.times.10.sup.1 nAs, showing
that the binding of the non-complementary probe was specific and
that the non-specific binding was low.
6.49. Preparation of Sheets of a Composite Electrode Containing
Fibrils and EVA
[0634] A composite electrode was prepared by compounding fibrils
with a polymer and compression molding the compounded material into
a sheet. Fibrils were compounded into EVA by using a Brabender
Plasticorder with a twin screw metering head at a temperature of
180 degrees centigrade and a speed of 100 r.p.m. 9.45 grams of
fibrils were dry blended with 25.55 grams of EVA (Quantum Chemical,
Microthene, FS-532). The blended materials were added to the mixing
head over a period of 1 minute to allow the material to melt.
Mixing was continued for an additional 5 minutes and then the
composite was removed from the mixing head and allowed to cool. To
prepare sheets of the composite for use as an electrode, a 2 gram
piece of the compounded material was assembled into a sandwich
between two polished stainless steel plates (triple plated
ferrotype plates, Testrite Company) and the assembly was placed
between heated platens set at 180 degrees Centigrade in a hydraulic
press (Carver). After allowing time for the material to be heated,
the composite was pressed into a flat sheet at 10000 pounds total
pressure. The assembly was then removed from the press and allowed
to cool to room temperature. The assembly was separated and a flat
disk with nominal thickness of 20 mils was removed.
6.50. Oxidation of Fibril-Polymer Composites by Chromic Acid
[0635] Composites of carbon fibrils (27% by weight) with ethyl
vinylacetate (fibril-EVA) and carbon fibrils with polyethylene
(fibril-PE) were used. The composites were obtained as 3'' disks
that were approximately 1 mm thick. Both fibril-EVA and fibril-PE
composites were oxidized by floating the disks on a solution
containing chromic acid (CrO.sub.3, H.sub.2O and H.sub.2SO.sub.4
(29/42/29; w/w/w)), at room temperature for 1 hour. After reaction
with the chromic acid solution, the oxidized composites were then
washed 4-5 times with deionized water, soaked for at least 5
minutes in deionized water and dried in air for 1 hour.
6.51. Derivatization of a Fibril-Polymer Composite with a Mixture
of Sulfuric and Nitric Acids
[0636] A composite of EVA and carbon fibrils (in the form of a 3''
diameter flat disk) was treated with a mixture of sulfuric acid and
nitric acid with 1:1 ratio (12 mL) for 3 hours. The treated
composite was washed with water. To the treated composite in a
mixture of water (150 mL) and ammonium hydroxide (30%, 150 mL) was
added sodium dithionite (10 grams). The reaction mixture was
refluxed for 2 hours. The composite was washed extensively with
water.
6.52. Preparation of a Fibril Composite Electrode with Exposed
Hydroxyl Groups
[0637] Hydroxyl groups were exposed on fibril-EVA composites by
hydrolysis of acetate groups at and near the surface of the
composite. Discs (3'' diameter, 0.01'' thickness) of the composite
material (27% CC fibrils in EVA, by weight) were immersed in 100 mL
of a 2 M solution of NaOH for 17-20 hours at room temperature. This
treatment leads to the exposure of hydroxyl groups on both sides of
the composite. The composite was washed with water and methanol and
then allowed to dry in air.
6.53. Immobilization of streptavidin on Oxidized Fibril-Polymer
Composites
[0638] EVA-fibril composites were oxidized as described in example
6.50 or by exposure to an oxygen plasma. The oxidized 3'' disc
composites were dried under vacuum pump for 1 hour and soaked
overnight (with shaking) in 25 ml of dichloromethane containing 0.1
M EDC (1-ethyl-3-(3-dimethylaminopropyl(carbodiimide) and 0.1 M
N-hydroxysuccinamide. The NHS activated composites were washed with
dichloromethane, methanol, deionized water and methanol, then
allowed to dry at room temperature.
[0639] For immobilization of streptavidin, the NHS activated
composites were rinsed with deionized water and floated on 6 mL of
streptavidin solution so that the NHS-ester activated surface faced
down. The streptavidin solution was prepared in PBS-1 (0.1 M sodium
phosphate, 0.15 M sodium chloride, pH=7.8) in a concentration of
0.7 mg/ml. The composite was shaken for 3 hours in the streptavidin
solution and washed by shaking in 20 ml of PBS-1 containing 0.1%
Triton for 30 minutes (one time) and in 20 ml of PBS-1 for 30
minutes (5 times). The streptavidin loaded EVA composites were
stored in PBS-1 at 4.degree. C.
6.54. Immobilization of Proteins on Fibril-Polymer Composites Via
SMCC Activation
[0640] A 3'' diameter disc of EVA-fibril composite that had been
treated with a mixture of nitric and sulfuric acids (as in Example
6.51) was placed in 15 mL of sodium phosphate buffer (0.1 M, pH
7.5).
Sulfosuccinimididyl-4-(N-maleimidomethyl)-cyclohexane-1-carboxylate
(sulfo-SMCC, 10 mg) was added and the reaction mixture was
incubated for 3 hours at room temperature. The reaction was stopped
and the composite was washed with sodium phosphate buffer. To a
solution of streptavidin (4.5 mg) in 0.1 M sodium phosphate, 20 mM
EDTA, pH 7.5 (300 mL), was added Traut's reagent (19.8 mL, 2.8
mg/mL). The reaction mixture was incubated at room temperature for
1 hour and 30 minutes. The sulfhydryl-labeled Streptavidin was
purified using a PD-10 (Pharmacia) disposable size exclusion column
(collected in a 3.5 mL fraction). The SMCC-treated composite (1
inch, derived via nitration/reduction of EVA CC composite) was
placed in the solution containing sulfhydryl-labeled streptavidin
(3.5 mL) and incubated with shaking for overnight at 4.degree. C.
The resulting streptavidin-coated composite was washed (5.times.20
minutes) by shaking in 0.1 M sodium phosphate, pH 7.5, containing
1% Triton X-100.
6.55. Immobilization of Streptavidin on a Composite Electrode
Presenting Exposed Hydroxyl Groups
[0641] Streptavidin was immobilized on a fibril-EVA composite that
presented hydroxyl groups at and near the surface. The protein was
immobilized after activation of the hydroxyl groups with
carbonyldiimidazole (CDI). Fibril-EVA composite electrodes that had
been treated with NaOH to expose hydroxyl groups (by the procedure
described in Example 6.52) were dried under vacuum. The dry
composite was immersed in 50 mL of anhydrous methylene chloride in
a dry glass jar. To the solution was added 100 mg (0.6 mmol) of
1,1'-carbonyldiimidazole (CDI) and the jar was gently rocked for 1
h at room temperature. The composite was then washed with methylene
chloride and methanol and then allowed to dry in air. The CDI
activated composite was cut (using a punch) into 3/16'' discs (96
total). Each disc was placed at the bottom of the well of a 96 well
microtiter plate. Streptavidin (100 mL of a 0.1 mg/mL solution in
0.2 M sodium bicarbonate, pH 8.5) was then added to each well. The
immobilization was allowed to proceed for 18-20 h at 4.degree. C.
The discs were washed three times by soaking in 100 ml portions of
50 mM sodium phosphate, pH 7.5 and stored in 100 mL of 50 mM sodium
phosphate, pH 7.2 until used.
6.56. Assay for AFP on a Composite Electrode of EVA and Fibrils
[0642] The AFP assay was performed using an EVA-fibril composite
electrode with streptavidin immobilized on it (prepared as
described in Example 6.53). The assay was carried out in a
ninety-six well plate that was preblocked with 1% BSA solution (1%
BSA and 0.3% Tween 20 in 0.1 M sodium phosphate, pH=6.8) and rinsed
once with 0.3% Tween 20 in 0.1 M sodium phosphate, pH=6.8, prior to
the assay. Forty eight discs with diameters of 3/16'' were punched
from a 3'' diameter EVA-SA composite and placed in the ninety-six
well plate with the treated surfaces up. Fifty microliters of
biotinylated AFP antibody were added to the wells that contained
composites. The plate was then shaken at room temperature for 30
minutes. The composites were rinsed twice with 0.1 mL of PBS-1 and
shaken for 1 hour at room temperature with the mixture of 0.05 mL
of calibrators and 0.05 mL of TAG1 labeled antibody. At the end of
the reaction, composites were rinsed with 0.150 mL of ECL assay
buffer and stored in protein buffer (3% BSA, 3% Tween 20, 25 mM
sodium chloride and 0.1 M sodium phosphate, pH=7.3) until the ECL
was measured. We used eight AFP calibrators ranging from 0.56 to
7950 IU/ml. Each calibrator was assayed in six replicates. FIG. 53
shows the results.
6.57. ECL Assay for TSH Using a Composite Electrode of EVA and
Fibrils
[0643] The assay was conducted using 3/16'' diameter
streptavidin-coated discs of EVA-fibril composite (prepared as
described in Example 6.55). The assay reagents were part of a TSH
assay kit (IGEN, Inc.) and included a biotin-labeled anti-TSH
antibody and a TAG1-labeled anti-TSH antibody, each dissolved in a
buffer (TSH Assay Diluent). The discs were placed into individual
wells of a 96-well microtiter plate. The biotin-labeled antibody
(0.05 mg, 0.012 mg/mL) was added to each well and the plate was
gently shaken for 30 minutes at 37.degree. C. After washing the
discs with TSH Assay Diluent, solutions containing the TAG1-labeled
antibody (0.025 mL, 600 ng/mL) and varying amounts of TSH were
added and the plate shaken another 60 minutes at 37.degree. C. The
discs were washed with and stored in TSH Assay Diluent until their
analysis by ECL.
6.58. DNA Hybridization Assay on a Fibril-Polymer Composite
[0644] This example describes an assay for a sequence of DNA. The
assay involves the formation of a sandwich complex on a
streptavidin-coated composite electrode which includes a
biotin-labeled capture probe (SC5), an analyte (SC3.1) and a
TAG1-labeled probe (SC4.1). SC3.1 and SC4.1 are described in
Example 6.48. SC5 was purchased from Oligos, Etc., Inc. and has the
sequence 5'-ca gtt gtg tgc cac cta caa gca tta cgg act agt cat ggt
tca cag agg-3'-biotin. Oxidized fibril-EVA composites were
activated with EDC and NHS as described in Example 6.53. Wells were
defined above 3/8'' discs of the composite by sealing the discs,
with O-rings, against holes drilled through a block of plastic. The
O-rings defined the area of the composite (0.25 cm.sup.2) in
contact with solution placed in the wells. Streptavidin was
immobilized on the discs by adding 0.05 mL of a 0.5 mg/mL solution
of Streptavidin (in PBS) to each well. The reaction was allowed to
proceed for 3 hours at room temperature while shaking the
apparatus. The discs were washed twice with PBS, once with PBS
containing 0.10% (w/v) Triton x-100 and twice more with PBS.
[0645] To capture the biotin labeled oligo we added 10.sup.13
molecules of SC5 in 0.05 mL of ECL Assay Buffer (IGEN, Inc.) and
incubated for 2 hours at room temperature with vigorous shaking.
Excess SC5 was removed by washing with PBS, PBS containing 0.10%
(w/v) Triton x-100, and ECL Assay Buffer. SC4.1 (10.sup.12
molecules in 0.025 mL) and SC3.1 (varying amounts in 0.025 mL) in
ECL Assay Buffer were then added. The hybridization reactions were
allowed to proceed for 4 hours. Excess reagents were then removed
by washing with PBS, PBS containing 0.10% (w/v) Triton X-100 and
ECL Assay Buffer. The discs were then placed in an ECL apparatus
and the ECL signal was measured. FIG. 54 shows the ECL signal as a
function of the amount of SC3.1.
6.59. Measurement of the Surface Area of a Fibril-Composite
Electrode
[0646] The amount of fibrils protruding from the surface of a
composite electrode can be estimated from measurements of the
double layer capacitance. Electrodes were prepared by punching out
0.25 inch diameter disks of composite and making electrical contact
to one surface by attaching a copper wire with electrical paint.
Any exposed copper wire was sealed in epoxy. The electrodes were
used to record cyclic voltammograms in argon-purged 0.5M
K.sub.2SO.sub.4 at several potential scan rates (e.g. 5, 10 and 25
mV/second) between -0.2V vs, Ag/AgCl and +0.8V vs. Ag/AgCl. The
double layer charging current, I.sub.dl was measured in the broad,
flat region of the cyclic voltammograms, typically at +0.25V vs.
Ag/AgCl. The slope of plots at I.sub.dl vs. scan rate is taken as
the double layer capacitance C.sub.dl. Using an average value of 10
.mu.F/cm.sup.2 of fibril surface area, and a fibril surface area of
200 M.sup.2/gram, the amount of fibrils exposed to the electrolyte
can be estimated.
6.60. Preparation of NHS Ester-Functionalized Fibrils
[0647] N-Hydroxysuccinimide (NHS) (0.35 g) and
1-ethyl-3-(3-dimethylaminopropyl) cardodiimide (EDC) (0.60 mg) were
added to a suspension containing 220 mg of carboxylated fibrils
(provided by Hyperion Catalysts Inc.) in 25 mL of dioxane and the
mixture was sonified (Sonifier 250, Branson Ultrasonics) for 5
minutes and stirred at room temperature overnight. The reaction was
stopped by vacuum filtration of the reactants from the fibrils in a
sintered glass funnel. The fibrils were washed with dioxane
(3.times.15 mL) and methanol (extensively) then dried under vacuum
to yield 220 mg NHS ester-activated fibrils.
6.61. Conjugation of Streptavidin to NHS Ester Fibrils
[0648] NHS Ester-modified fibrils (2.1 mg, prepared as described in
Example 6.60) were sonified (Sonifier 250, Branson Ultrasonics) in
400 .mu.L PBS-1 buffer (0.1 M sodium phosphate, 0.15 M sodium
chloride, pH=7.8) for 5 minutes at the lowest power setting. A
solution of streptavidin (2.4 mg in 150 .mu.L PBS-1) was mixed with
the dispersed fibril suspension and the mixture (650 .mu.L) was
gently shaken for 3 hours at room temperature. The fibrils were
washed by multiple cycles of repetitive centrifugation, and
resuspension using the following buffers in series: 0.1 M sodium
phosphate containing 1% Triton X-100 (1 time), PBS-1 (two times),
0.1 M sodium phosphate containing 0.1% Triton X-100 (1 time), and
PBS-1 (4 times). Streptavidin loaded fibrils were stored at
4.degree. C. in PBS-1.
6.62. Fabrication of a Ultra Thin Fibril Mat (UTFM) on a Nylon
Membrane Filter
[0649] An aqueous suspension containing CC fibrils at a
concentration of 0.1 mg/mL was prepared by diluting a stock
suspension of the CC fibrils (1 mg/mL in water) into an aqueous
solution of Triton X-100 (0.2% (w/v)). The CC fibrils were finely
dispersed with a probe sonicator (Sonifier 250, Branson
Ultrasonics) by sonicating for 5 min using a duty cycle of 30% and
setting the output control to a value of 3. A further dilution of
the sonified suspension to a concentration of 0.01 mg/mL was then
carried out by diluting 4 mL of the suspension up to a volume of 40
mL with the aqueous solution of Triton X-100.
[0650] A UTFM was prepared on a nylon membrane (0.45 mm pore size,
47 mm diameter) by vacuum filtration (see FIG. 24 for an example of
an apparatus for filtration of fibril mats). The finely dispersed
fibrils were filtered onto the nylon membrane in four aliquots of 4
mL each using a vacuum of approximately 26 in. of Hg. Vacuum
filtration was continued until only a trace of liquid remained
unfiltered above the membrane (by visual observation). The mat was
then removed from the filtration apparatus, compressed between two
pieces of clean, dry filter paper, and allowed to dry flat in an
oven for approximately 10-15 minutes at 60.degree. C.
[0651] The volumes used could be scaled accordingly for electrodes
of different areas and/or thickness.
6.63. A Nucleic Acid Hybridization Assay on a Bilaver Ultra Thin
Fibril Mat Electrode
[0652] Streptavidin was covalently immobilized on dispersed CC
carbon fibrils as described in Example 6.61. A total of 100 .mu.g
of these fibrils were suspended in a solution containing BSA at a
concentration of 1 mg/mL (w/v) to block unoccupied sites on the
fibrils. The blocked fibrils were then centrifuged and resuspended
in 1 mL of deionized water. This suspension was redispersed by
sonification (Sonifier 250, Branson Ultrasonics) for 5 minutes.
[0653] An ultra-thin fibril mat (UTFM) was prepared as described in
Example 6.62. After the UTFM was prepared, the second layer was
formed by the filtration of 17 .mu.L of the suspension of
streptavidin-fibrils onto the first layer under the same conditions
as used in Example 6.62.
[0654] To conduct the DNA hybridization assay, we used a "capture"
oligonucleotide (28 base pairs, biotinylated at the 5' position)
that was allowed to hybridize to a complementary "TAGged"
oligonucleotide (28 base pairs, end labeled with TAG1-NHS Ester).
The assay was prepared by the following steps: i) calibration
solutions were prepared that contained variable concentrations of
the biotin-labeled oligo and a constant excess (10.sup.12
molecules) of the TAG1-labeled oligo; ii) the calibration solutions
(50 .mu.L) were filtered through ultra-thin fibril mats (one UTFM
per solution) at a flow velocity of 50 .mu.m/sec to allow capture
of the biotinylated complex onto the streptavidin-coated fibrils in
the fibril mat; iii) the UTFM was washed with 50 .mu.L of ECL Assay
Buffer (IGEN, Inc.) to remove unbound reagents, and iv) the UTFMs
(and the attached oligonucleotide complexes) were transferred to a
measurement cell (FIG. 34) and ECL was measured. FIG. 55 shows that
the assay measured the TAG1-labeled oligonucleotide with high
sensitivity and produced a linear response over a wide dynamic
range.
6.64. A Sandwich Immunoassay for AFP on a Bilayer Ultra Thin Fibril
Mat Electrode
[0655] A suspension of streptavidin-coated (and BSA-blocked)
fibrils was prepared as described in Example 6.61. The suspension
was diluted in ECL Assay Buffer (IGEN, Inc.) to give a stock
suspension with a concentration of fibrils of 7 mg/mL. The solution
was placed in an ice water bath (to prevent denaturing of the
streptavidin) and the fibrils were redispersed by sonication
(Sonifier 250, Branson Ultrasonics) for 5 minutes using a duty
cycle of 20% and setting the output control to a value of 1.5.
[0656] A vacuum filtration apparatus was used to prepare bilayer
UTFM electrodes on nylon filter membranes (0.45 mm pore size). The
filtration apparatus defined a 1/8'' diameter area on the membrane
through which filtration occurred. A layer of underivatized fibrils
was formed by filtering (using suction) 87.5 .mu.L of a finely
dispersed suspension containing underivatized fibrils at a
concentration of 0.01 mg/mL (prepared as described in Example
6.62). A second layer was formed by filtering 50 .mu.L of the stock
suspension of streptavidin-coated fibrils onto the layer of
underivatized fibrils.
[0657] The AFP assay reagents (Elecsys, Boehringer-Mannheim) were
pre-mixed prior to filtration by combining 50 .mu.L of the stock
solution of the biotinylated AFP antibody, 50 .mu.L of the stock
solution of the TAG1-labeled AFP antibody, and 10 .mu.L of one of
several stock solutions containing known concentrations of AFP. The
combined solutions were then filtered by suction at a controlled
flow velocity using a vacuum pressure of 5 in. of Hg. Each sample
took between 30-50 minutes to filter. The mats were then washed
with 150 .mu.L of ECL Assay Buffer (IGEN, Inc.), removed and
allowed to dry. The mats were transferred to a measurement cell
(FIG. 34) and ECL was measured. FIG. 56 shows the ECL signal as a
function of the concentration of AFP in the calibration
solution.
6.65. Forming Conductive Films of Gold on Non-conductive Filter
Membranes
[0658] Nylon membrane filters from Whatman (0.45 .mu.m pore size)
were coated with sputtered gold using a Balzers MED 010
Minideposition System. The deposition was carried out using an
argon plasma (at a pressure of 5.times.10.sup.-2 mbar) and a
discharge current of 100 mA.
6.66. A Sandwich Immunoassay for AFP on an Ultra Thin Fibril Mat
Electrode Formed on a Gold-Coated Nylon Filter Membrane
[0659] A suspension of streptavidin-coated (and BSA-blocked)
fibrils was prepared as described in Example 6.61. The suspension
was diluted in ECL Assay Buffer (IGEN, Inc.) to give a stock
suspension with a concentration of fibrils of 28 mg/mL. The
solution was placed in an ice water bath (to prevent denaturing of
the streptavidin) and the fibrils were redispersed by sonication
(Sonifier 250, Branson Ultrasonics) for 5 minutes using a duty
cycle of 20% and setting the output control to a value of 1.5.
[0660] A total of thirty-six 5/16'' diameter disks were punched out
of A conductive Au-coated nylon filter membranes (100 nm gold film,
prepared as described in Example 6.65) was cut (using a hole punch)
to form 5/16'' diameter discs. The disks were placed into the wells
of a multiple sample filtration apparatus, which allows for as many
as ninety-six samples at a time to be filtered under a controlled
vacuum pressure. This apparatus filters samples onto a 3/16''
diameter circular region on each disc. Single layer UTFMs were
formed by filtering (using a vacuum of 26 in. of Hg) 82.5 .mu.L of
the stock solution of streptavidin-coated fibrils onto the discs.
The AFP assay reagents (Elecsys, Boehringer-Mannheim) were
pre-mixed prior to filtration by combining 50 .mu.L of the stock
solution of the biotinylated AFP antibody, 50 .mu.L of the stock
solution of the TAG1-labeled AFP antibody, and 10 .mu.L of one of
several stock solutions containing known concentrations of AFP. The
combined solutions were then filtered by suction at a controlled
flow velocity using a vacuum pressure of 5 in. of Hg. Each sample
took between 30 minutes to filter. Each mat was then washed with
150 .mu.L of assay buffer, then removed and stored in a protein
buffer which contains 3.0% BSA, 3.0% Tween-20, 25 mM NaCl, and 100
mM NaH.sub.2PO.sub.4. The mats were transferred to a measurement
cell (FIG. 34) and ECL was measured. FIG. 57 shows the ECL signal
as a function of the concentration of AFP in the calibration
solution.
6.67. AFP Assay on Two Different Electrodes: Voltammetric
Resolution of Signal and Background
[0661] The AFP assay was developed on two composite electrodes.
Both electrodes were prepared from an ethylene vinyl acetate (EVA)
copolymer containing 27% CC-fibrils by weight. One electrode (the
"hydrolyzed EVA" electrode) was treated with potassium hydroxide,
activated with CDI, and exposed to streptavidin (as in Example
6.55). The other electrode (the "chromic acid EVA" electrode) was
treated with chromic acid, treated with NHS and EDC and exposed to
streptavidin (as in Example 6.53).
[0662] Sandwich complexes containing a biotin-labeled anti-AFP
antibody, a TAG1-labeled anti-AFP antibody and AFP were captured on
3/16'' discs of the two electrodes by the procedures described in
Example 6.56.
[0663] Each electrode was installed in an ECL test cell (FIG. 34)
with a gasket (1/8'' id., 7/8'' od., and 0.017'' thick) which
defined the active area of the electrode (1/8'' diameter). The test
cell consisted of a black Delrin body that contained a three
electrode electrochemical cell and an optical window parallel with
the working electrode. The electrodes were a 3M Ag/AgCl reference
electrode, a platinum mesh counter electrode, and the fibril-EVA
composite as working electrode. The test cell was filled with ca. 1
mL of Assay Buffer and placed in a light-tight box that was heated
to ca. 33.degree. C. with a prototype electrical heater. The test
cell optical window was placed in front of a PMT and the box was
closed. The PMT was powered at 900 V with a Pacific Instruments
Model 126 Photometer running in analog mode with a 1 second time
constant filter using several of the photocurrent ranges (i.e. 10
nA/V, 30 nA/V, 100 nA/V, 300 nA/V, and 1000 nA/V). The
electrochemical cell was controlled by an EG&G PARC Model 175
Universal Programmer and an EG&G PAR Model 173
Potentiostat/Galvanostat. Following a 100 s delay at 0 V vs. 3M
Ag/AgCl the potential was swept at 100 mV/s from 0 V (E.sub.0), to
a lower limit of -0.8 V (E.sub.1), an upper limit of 2.3 V
(E.sub.2) and an ending potential of 0 V (E.sub.3). The current
range was set at 1 mA/V. The air temperature around the test cell
was measured with a Cole Parmer Thermistor Thermometer and probe.
All analog data (temperature, light, applied potential, and
current) was digitized at 10 Hz with a Computer Boards Inc.
CIO-DAS1602/16 A/D board controlled by HEM Data Corp. Snap-Master
for Windows J in a Pyramid 100 MHz Pentium computer. From the raw
data, plots of ECL and voltammetric current vs. applied potential
were prepared and several data were calculated including: maximum
anodic current, ECL peak potential (applied potential at the ECL
peak), mean ECL dark current (mean light between starting potential
and 0.5 V), and dark corrected integrated ECL (the difference
between the average ECL over a given potential range and the mean
dark all of which was then multiplied by the duration in seconds of
the given potential range).
[0664] The voltammetry from the AFP assays are dependent upon the
electrode used. The voltammograms for the AFP assay on hydrolyzed
EVA consist of an irreversible oxidative wave starting at 1.4 V and
having an anodic peak at ca. 1.8 V. The maximum anodic current
occurs at 2.3 V. Little current is passed between -0.8 V and 1.4 V.
The voltammograms from chromic acid treated EVA consist of a very
broad irreversible oxidative wave starting at 0.7 V and having
several undefined anodic peaks (ca. 1.1, 1.5, and 2.0 V) and a
maximum anodic current at 2.3 V. Little current was passed between
-0.8 and 0.7 V.
[0665] The hydrolyzed EVA yielded ECL traces consisting of a peak
at with a small amount of tailing to the high potential side. The
peak potentials shifted slightly from 1.85 V for blank signals to
1.75 V for analyte signals. The chromic acid treated EVA yielded
two closely spaced peaks, both of which scaled with analyte
concentration. These peaks were at ca. 1.6 V and ca. 1.25 V. At low
analyte concentrations the peak at 1.6 V was dominant while at
higher analyte concentrations the peak at 1.25 V was dominant. The
chromic acid treatment increased the peak-to-peak resolution from
ca. 100 mV (hydrolyzed EVA) to ca. 350 mV. This peak shift was
sufficient to allow the analysis of the first peak which has been
shown to be more sensitive to analyte and to reduce the amount of
the blank signal used in the analysis.
[0666] In similar experiments, we compared the ECL traces for AFP
calibrator 1 (predominantly ECL assay buffer, FIG. 60) and AFP
calibrator 3 (FIG. 61). In FIG. 60, the ECL signal corresponding to
assay buffer appears as a peak with a maximum at 1.5V. In FIG. 61,
the ECL signal for assay buffer is also at 1.5V; the additional
peak at 1.0V corresponds to the signal from the analyte in a
sandwich complex that includes a TAG1-labeled complementary
antibody.
6.68. Preparation of Extruded Sheets of Fibril-EVA Composites
[0667] We blended 270 grams of carbon nanotubes (HCI Fibrils, CC
grade) and 730 grams of ethyl vinylacetate (EVA, Quantum Microthene
FE530) in a Henschel lab mixer for 2 minutes. The nanotube-EVA
blend was vacuum transferred to a sealed hopper, compounded on a
Buss PR 46 kneader at 180.degree. C., and fed into a Buss cross
head pelletizer. The pellets were dried in a Gala dryer. This
process gave a composite containing 27% fibrils by weight.
[0668] Prior to extrusion, pellets of compounded nanotube-EVA
composite were dried at 80.degree. C. for at least 12 hours. The
dried pellets were starve fed into a Brabender PL2000 Plasti-Corder
(a 3/4'' 25:1 L/D single screw extruder equipped with a 2:1
compression ratio screw and a 6'' flex-lip die). The temperature of
the three heating zones of the extruder and the die was 245.degree.
C. The output die of the extruder produced a continuous ribbon
(.about.15 cm wide, .about.1 mm thick) of nanotube-EVA composite
that was collected on a conveyor belt at ambient temperature with
negligible draw down. The surface of the composite that did not
contact the conveyor belt was used for all further experiments.
6.69. Use of Oxygen Plasma to Chemically Modify Fibril Composites
for ECL Immunoassays
[0669] Composites of carbon fibrils and EVA (27% fibrils by weight)
were exposed to a plasma formed from oxygen (O.sub.2) gas. The
composites were exposed to the plasma for 10 minutes at 2000 W (20
kwmin). To introduce N-hydroxysuccinimide-ester functional groups
(NHS-ester), the plasma-treated fibril-EVA composites (126
cm.sup.2) were reacted with N-hydroxysuccinimide (700 mg, from
Aldrich 13067-2) and 1-(3-dimethylaminopropyl)-3-ethylcarbodiimide
hydrochloride (1.6 g, from Aldrich 16146-2) in anhydrous methylene
chloride (50 mL) for 2 hours at room temperature, then rinsed with
methanol and water, and blown dry with a stream of argon gas. The
NHS-ester derivatized composites were incubated with streptavidin
(5 mg, from Pierce 21125) in PBS-1 buffer (0.1 M sodium phosphate,
0.15 M sodium chloride, pH=7.8, 50 mL) for 4 hours at room
temperature. Then the composites were washed with 1% Triton X-100
in PBS-1 for 30 minutes shaking and three times with PBS-1 for 30
minutes shaking each.
6.70. Use of oxygen Plasma (40 KWmin) Followed by NH.sub.3/N.sub.2
Plasma (4:1, 120 KWmin) to Chemically Modify Fibril Composites
[0670] Composites (123 cm.sup.2) of carbon fibrils and EVA (27%
fibrils by weight) were first exposed to a plasma formed from
oxygen (O.sub.2) gas. The composites were exposed to the plasma for
20 minutes at 2000 W (40 kwmin). Then the composites were exposed
to a plasma formed from a mixture of ammonia (NH.sub.3) gas and
nitrogen (N.sub.2) gas (4:1 ratio of the gases respectively). The
composites were exposed to this plasma for 60 minutes at 2000 W
(120 kwmin). To form a maleimide functional group, the
plasma-treated fibril-EVA composites were incubated with Sulfo-SMCC
(35 mg, from Pierce: 22322) in PBS-1 (50 ml) for 3 hours with
shaking at room temperature. Then the composites were washed once
with water (60 ml with 10 minutes shaking) and three times with
PBS-1 (60 ml with 10 minutes shaking each).
[0671] To prepare IgG for immobilization on the activated
composites, dithiothreitol (5 mg, from Sigma D-9779) was added to
anti-AFP IgG (from Boehringer Mannhem) solution (5.5 mg in 500
.mu.l PBS-1 buffer). The mixture was incubated for 30 minutes (with
rotating to mix) at room temperature. This procedure exposed thiol
groups on the IgG ("IgG-(SH).sub.n"). The "IgG-(SH).sub.n" was
purified by column chromatography, and then diluted into 20 mM EDTA
PBS-1 buffer.
[0672] The maleimide-activated composite (60 cm.sup.2) was
incubated with the purified "IgG-(SH).sub.n" solution (5.5 mg
"IgG-(SH).sub.n" in 30 ml of 20 mM EDTA PBS-1 buffer) for 2.5 hours
at room temperature. The composite was washed once with 1% Triton
X-100 (60 ml) for 20 minutes with shaking and three times with
PBS-1 for 20 minutes each with shaking. The anti-AFP-IgG composite
was stored in PBS-1.
[0673] An AFP assay was performed on the anti-AFP-IgG composites. A
96-well plate was precoated with BSA. Individual disks ( 3/16''
diameter) of the composites were punched out by hand with a metal
punch. Each disk was incubated with a solution containing
TAG1-labeled IgG (100 .mu.L) and a sample containing a known amount
of AFP (20 .mu.L) for 60 minutes at room temperature. After
incubation, the disks were rinsed three times with PBS-1 (200
.mu.L) and stored in BSA assay diluent (100 .mu.L). FIG. 62 shows a
plot of the log of the difference between the ECL signal for
samples containing AFP and a sample that contained no AFP (the
background sample) as a function of the log of the concentration of
AFP in the sample.
6.71. Adsorption of Proteins on Composite Electrodes that were
Oxidized in a Water/Argon Plasma
[0674] Fibril-EVA composites electrodes (prepared as described in
Example 6.68) were treated with a plasma formed from
water-saturated argon in an Advanced Plasma Systems Series C plasma
reactor (1 hour, 2000 W, 300 mtorr). A composite (.about.80
cm.sup.2) was placed in 20 mL of a solution containing an anti-AFP
monoclonal (Beohringer-Mannheim) at a concentration of 0.2 mg/mL in
100 mM phosphate, pH 7.5 and incubated with gentle agitation for 2
hours at room temperature. The composite was washed with 100 mM
phosphate, pH 7.5 and stored in the same solution at -4 C. The
amount of adsorbed antibody on the disk was determined, through the
use of radiolabeling, to be 2.9 pmol.
[0675] Sandwich immunoassays for AFP were conducted on these disks.
Samples (20 uL) containing AFP were combined with 50 uL of a
solution containing a TAG1-labeled secondary antibody
(Boehringer-Mannheim) at a concentration of 12 ug/mL. The surface
was treated with this mixture and then washed with phosphate
buffer. ECL was measured by contacting the composite electrode with
a solution containing tripropylamine (Assay Buffer, IGEN) and
scanning the potential at the composite electrode from 0 V to -0.8
V to 2.3 V (vs. Ag/AgCl) at a scan rate of 0.1 V/s. The ECL signals
observed for samples with known amounts of AFP are shown in FIG.
63.
6.72. AFP Assays Using Fibril-EVA Composite Electrodes Containing
15% Fibrils by Weight
[0676] Pellets of fibril-EVA composites containing a 27% fibrils by
weight were compounded with additional EVA to produce a fibril-EVA
composite containing 15% fibrils by weight. This composite was
extruded into sheets by a procedure analogous to that described in
Example 6.68. The composite was treated with an Argon/Water plasma
and coated with an anti-AFP antibody as described in Example 6.71.
Studies using a radiolabeled antibody showed that these composites
containing only 15% fibrils by weight adsorbed more antibody (3.13
pmol) than other composites containing 27% fibrils by weight (2.9
pmol, see Example 6.71). The antibody-coated composites were used
in AFP assays as described in Example 6.71. The ECL signals that
were observed for samples containing known amounts of AFP are shown
in FIG. 64. The composites containing only 15% fibrils by weight
gave slightly higher ECL signals (FIG. 64) than composites
containing 27% fibrils by weight (FIG. 63, Example 6.71).
6.73. Adsorption of Proteins on a Plasma-Grafted Layer of
Octadecylamine on a Plasma-Oxidized Composite
[0677] Fibril-EVA composites (prepared as described in Example
6.68) were soaked for 2 hours in a solution containing octadecyl
amine at a concentration of 1 mg/mL in chloroform. The composite
was dried in air (weight was applied at the edges to keep the sheet
of composite flat during the drying process). The composite was
then treated with an oxygen plasma in an Advanced Plasma Systems
Series C plasma reactor (30 min., 2000 W, 300 mtorr). The composite
was then coated with avidin by soaking the material in a solution
containing avidin (1.25 mg/mL) in 5 mM phosphate, pH 7.5. Excess
avidin was removed by washing with phosphate buffered saline.
Radioisotope experiments using .sup.125I-labeled streptavidin and
.sup.125I and biotin-labeled rabbit IgG showed that we immobilized
30-43 pmols of streptavidin and that the streptavidin was capable
of binding >2.2 pmol of biotin-labeled antibody.
[0678] Sandwich immunoassays for AFP were conducted on these disks.
The surface was treated with 100 uL of a solution containing a
biotin-labeled anti-AFP antibody (7 ug/mL, Boehringer-Mannheim) for
30 min. with shaking and then washed with phosphate buffered
saline. A 20 uL sample was combined with 100 uL of a solution
containing a TAG1-labeled secondary antibody (Boehringer-Mannheim)
at a concentration of 12 ug/mL. The surface was treated with this
mixture for 60 min while shaking and then washed with Assay Buffer
(IGEN). ECL was conducted by contacting the composite electrode
with a solution containing tripropylamine (Assay Buffer, IGEN) and
scanning the potential at the composite electrode from 0 V to -0.8
V to 2.3 V (vs. Ag/AgCl) at a scan rate of 0.1 V/s. The ECL signals
observed for samples with known amounts of AFP are shown in FIG.
65.
6.74. Coupling of Proteins to Functional Groups Grafted onto
Plasma-Treated Composites
[0679] Fibril-EVA composites (prepared as described in Example
6.68) were treated with an argon plasma in an Advanced Plasma
Systems Series C plasma reactor (1000 W, 3 min., 300 mtorr). The
composites were removed from the reactor and immediately placed in
oxygen-free solutions containing 4% (w/v) of acrylic acid
(distilled) or allyl amine in water. The composites were incubated
in these solutions for 3 hours at 30 C then washed extensively with
water and dried in air. Streptavidin was immobilized through
grafted and/or polymerized acrylic acid moieties by activating the
carboxylic acid groups as NHS esters by a method analogous to that
described in Example 6.69. Thiol-labeled streptavidin was
immobilized through grafted and/or polymerized allyl amine moieties
after introducing maleimide groups on the composite by a method
analogous to that described in Example 6.70. We showed that these
composites were capable of binding biotin-labeled reagents and were
capable of exciting ECL from ECL labels; we measured ECL from the
composite electrodes after treating the materials with an excess of
rabbit IgG that was labeled with biotin and TAG1 groups. ECL from
bound IgG was generated by contacting the composite electrode with
a solution containing tripropylamine (Assay Buffer, IGEN) and
scanning the potential at the composite electrode from 0 V to -0.8
V to 2.3 V (vs. Ag/AgCl) at a scan rate of 0.1 V/s. The acrylic
acid and allyl amine treated composites yielded, respectively,
integrated PMT currents of 203 nAs and 123 nAs.
6.75. Use of Plasma to Bond Avidin to Fibril Composites for ECL
Immunoassays
[0680] Plasma was used to fuse avidin to the surface of composite
material. The fusion was performed by first soaking a block of
fibril-EVA composite (example 6.68) composite in a solution of 0.5
mg/ml avidin for 3 hours. After washing with three changes of 60 ml
PBS-1, the composite was air dried, cut into strips and treated
with either Ar or O.sub.2 plasma for 5 minutes at 600 Watts (3000
Wmin). These experiments were conducted on a Series B plasma
Reactor (APS Technologies).
[0681] Following plasma treatment of the composite, 5/16'' disks
were punched out and the amount of active avidin immobilized was
measured by radiolabeling experiments that used binding
biotinylated .sup.125I-IgG. Composites with avidin bonded to their
surfaces bound 0.244 pmole (Ar plasma treated) and 1.899 pmole
(oxygen plasma treated) of IgG.
[0682] Binding assays using biotinylated-TAG1-IgG (BTI) were also
performed. BTI was used at a concentration of 41 nM and the amount
bound was quantitated by ECL. In the case of O.sub.2 plasma fused
avidin, 4 .mu.M d-biotin was incubated with some of the chips for 1
hour prior to the incubation with BTI. This was done in order to
evaluate the amount of binding that was due to the interaction
between biotin and avidin. The measured ECL: signals for Ar plasma
and O.sub.2 plasma were 10424 nAsec and 8179 nAsec,
respectively.
6.76. Use of Plasma to Bond Affinity Matrices to Fibril
Composites
[0683] Acrylic beads (125 mg) bearing biotin (Sigma#B-3272,
lot#57F4034) were ground finely. This powder was suspended in
approximately 20 ml of de-ionized water and mixed well on a
vortexer; the suspension was removed and filtered though a 0.45
micron filter (Gelman Sciences #4598). The filtered suspensions
were dried on several 5/16''-diameter disks of a fibril-EVA
composite (27% fibrils by weight, see example 6.68).
[0684] Some of the disks were plasma treated with O.sub.2 plasma
for 10000 Wmin; others were plasma treated with O.sub.2 for 120000
Wmin. After plasma treatment, the disks were washed 3 times for 10
min in PBS-1 and then rinsed 3 times with PBS-1 to remove any
unbound fragments.
[0685] After washing, the derivatized composites were incubated
with 0.2 mg/ml streptavidin for 2 hours at room temperature, rinsed
and stored in PBS-1 buffer. Disks ( 3/16'' diameter) of
streptavidin-coated composites were punched out and placed in the
wells of a 96-well plate. A solution containing biotinylated
anti-AFP antibody was added to each well. The disks were incubated
with shaking for 30 min, then washed with PBS-1 buffer. 100 .mu.l
of TAG1-labeled anti-AFP antibody and 20 .mu.l of samples
containing known concentrations of AFP were added to the wells and
incubated for 1 hr at room temperature with shaking. The disks were
then rinsed 3 times with assay buffer and ECL was measured as
described in Example 6.71. FIG. 66 shows a plot of the log of the
ECL signal as a function of the concentration of AFP in the
samples.
6.77. ECL-Based Binding Assays Using Dried Reagents and not
Requiring a Wash Step
[0686] Fibril-EVA composite (prepared as described in Example 6.68)
was oxidized in an oxygen plasma and coated with streptavidin (as
described in Example 6.69). The composite electrode was cut into
5/16'' diameter disks that were placed in holders that allowed one
surface of the disks to be placed in contact with solutions. The
disks were treated with 100 uL of a solution containing a
biotin-labeled anti-AFP antibody (7.5 ug/mL, Boehringer-Mannheim)
for 1 hour with agitation and then washed with phosphate-buffered
saline. The other reagents required for the assay were then dried
on the surfaces by adding and lyophilizing the following solution:
TAG1-labeled anti-AFP antibody (12 ug/mL, Boehringer-Mannheim),
phosphate (200 mM), tripropylamine (200 mM), bovine serum albumin
(2%), sucrose (2%), chloroacetamide (0.1%), and Triton X-100
(0.02%), pH of 7.6. AFP assays were conducted by adding a 95 uL
sample to the dried reagents on the surface of the disks and
incubating for 1 hour while shaking. ECL was excited by inserting a
counter and reference electrode into the solution above the
composite electrodes and scanning the potential at the counter
electrode from 0 V to -0.8 V to 2.3 V (vs. Ag/AgCl) at a scan rate
of 4.8 V/s. FIG. 67 shows the ECL signals measured at a
photomultiplier tube for solutions containing known amounts of
AFP.
7. INCORPORATION OF REFERENCES
[0687] The present invention is not to be limited in scope by the
specific embodiments described herein. Indeed, various
modifications of the invention in addition to those described
herein will become apparent to those skilled in the art from the
forgoing description and accompanying figures. Such modifications
are intended to fall within the scope of the claims. Various
publications are cited herein, the disclosures of which are
incorporated by reference in their entireties.
* * * * *